U.S. patent application number 14/194566 was filed with the patent office on 2014-06-26 for nucleic acid sample preparation.
This patent application is currently assigned to Biological Dynamics, Inc.. The applicant listed for this patent is Biological Dynamics, Inc.. Invention is credited to David CHARLOT, Irina DOBROVOLSKAYA, Rajaram KRISHNAN, Lucas KUMOSA, James MCCANNA, Paul SWANSON, Eugene TU, Robert TURNER, Kai YANG.
Application Number | 20140174931 14/194566 |
Document ID | / |
Family ID | 49325450 |
Filed Date | 2014-06-26 |
United States Patent
Application |
20140174931 |
Kind Code |
A1 |
KRISHNAN; Rajaram ; et
al. |
June 26, 2014 |
NUCLEIC ACID SAMPLE PREPARATION
Abstract
The present invention includes methods, devices and systems for
isolating a nucleic acid from a fluid comprising cells. In various
aspects, the methods, devices and systems may allow for a rapid
procedure that requires a minimal amount of material and/or results
in high purity nucleic acid isolated from complex fluids such as
blood or environmental samples.
Inventors: |
KRISHNAN; Rajaram; (San
Diego, CA) ; CHARLOT; David; (San Diego, CA) ;
TU; Eugene; (San Diego, CA) ; MCCANNA; James;
(San Diego, CA) ; KUMOSA; Lucas; (Centennial,
CO) ; SWANSON; Paul; (Santee, CA) ; TURNER;
Robert; (San Diego, CA) ; YANG; Kai; (San
Diego, CA) ; DOBROVOLSKAYA; Irina; (San Diego,
CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Biological Dynamics, Inc. |
San Diego |
CA |
US |
|
|
Assignee: |
Biological Dynamics, Inc.
San Diego
CA
|
Family ID: |
49325450 |
Appl. No.: |
14/194566 |
Filed: |
February 28, 2014 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
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14067841 |
Oct 30, 2013 |
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14194566 |
|
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08603791 |
Feb 20, 1996 |
5828770 |
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14067841 |
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Current U.S.
Class: |
204/547 |
Current CPC
Class: |
B01L 2400/0424 20130101;
G01S 5/163 20130101; B01L 2300/0645 20130101; C12N 15/101 20130101;
C12N 15/1003 20130101; B03C 7/023 20130101; G06F 3/0346 20130101;
B01L 3/502715 20130101; B01L 7/52 20130101; B01L 2300/0636
20130101; B03C 2201/26 20130101; C12Q 1/6806 20130101; B03C 5/005
20130101; B03C 5/026 20130101; G01N 27/447 20130101; B01D 57/02
20130101; G01N 27/44704 20130101; G01S 11/12 20130101; C12Q 1/6806
20130101; C12Q 2523/307 20130101 |
Class at
Publication: |
204/547 |
International
Class: |
C12Q 1/68 20060101
C12Q001/68; B03C 7/02 20060101 B03C007/02 |
Claims
1. A method for isolating a nucleic acid from a fluid, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes capable of establishing an AC
electrokinetic field region; b. concentrating cells and/or other
particulate material in the fluid in a first AC electrokinetic
field region, wherein the first AC electrokinetic field region is a
first dielectrophoretic high field region and the conductivity of
the fluid is less than 500 mS/m; c. isolating nucleic acid in a
second AC electrokinetic field region, wherein the second AC
electrokinetic field is a second dielectrophoretic high field
region; and d. flushing the concentrated cells and/or other
particulate material from the first AC electrokinetic field
region.
2. The method of claim 1, wherein the AC electrokinetic field is
produced using an alternating current having a voltage of 1 volt to
40 volts peak-peak, and/or a frequency of 5 Hz to 5,000,000 Hz and
duty cycles from 5% to 50%.
3. The method of claim 1, wherein the conductivity of the fluid is
less than 300 mS/m.
4. The method of claim 1, wherein the electrodes are selectively
energized to provide the first dielectrophoretic high field region
and subsequently or continuously selectively energized to provide
the second dielectrophoretic high field region.
5. The method of claim 1, wherein the array of electrodes is
spin-coated with a hydrogel having a thickness between about 0.1
microns and 1 micron.
6. The method of claim 5, wherein the hydrogel comprises two or
more layers of a synthetic polymer.
7. The method of claim 5, wherein the hydrogel has a viscosity
between about 0.5 cP to about 5 cP prior to spin-coating.
8. The method of claim 5, wherein the hydrogel has a conductivity
between about 0.1 S/m to about 1.0 S/m.
9. The method of claim 1, wherein the isolated nucleic acid
comprises less than about 10% non-nucleic acid cellular material or
cellular protein by mass.
10. The method of claim 1, wherein the method is completed in less
than 10 minutes.
11. The method of claim 1, wherein the array of electrodes
comprises a wavy line configuration, wherein the configuration
comprises a repeating unit comprising the shape of a pair of dots
connected by linker, wherein the linker tapers inward toward the
midpoint between the pair of dots, wherein the diameters of the
dots are the widest points along the length of the repeating unit,
wherein the edge to edge distance between a parallel set of
repeating units is equidistant, or roughly equidistant.
12. The method of claim 1, wherein the array of electrodes
comprises a passivation layer with a relative electrical
permittivity from about 2.0 to about 4.0.
13. The method of claim 1, wherein the fluid is a bodily fluid, an
environmental sample, food or beverage, growth medium or water.
14. A method for isolating a nucleic acid from a fluid, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes capable of establishing an AC
electrokinetic field region; b. concentrating cells and/or other
particulate material in the fluid in a first AC electrokinetic
field region, wherein the first AC eletrokinetic field region is a
first dielectrophoretic high field region and the conductivity of
the fluid is less than 500 mS/m; c. isolating nucleic acid in a
second AC electrokinetic field region, wherein the second AC
electrokinetic field is a second dielectrophoretic high field
region; d. flushing the concentrated cells and/or other particulate
material from the first AC electrokinetic field region; e.
degrading residual proteins and/or material; and f. flushing the
degraded residual proteins and/or material from the isolated
nucleic acid.
15. The method of claim 14, wherein the residual proteins and/or
material are degraded by chemical and/or enzymatic degradation
agents.
16. The method of claim 14, wherein the AC electrokinetic field is
produced using an alternating current having a voltage of 1 volt to
40 volts peak-peak, and/or a frequency of 5 Hz to 5,000,000 Hz and
duty cycles from 5% to 50%.
17. The method of claim 14, wherein the electrodes are selectively
energized to provide the first dielectrophoretic high field region
and subsequently or continuously selectively energized to provide
the second dielectrophoretic high field region.
18. The method of claim 14, wherein the array of electrodes is
spin-coated with a hydrogel having a thickness between about 0.1
microns and 1 micron.
19. The method of claim 14, wherein the array of electrodes
comprises a wavy line configuration, wherein the configuration
comprises a repeating unit comprising the shape of a pair of dots
connected by linker, wherein the linker tapers inward toward the
midpoint between the pair of dots, wherein the diameters of the
dots are the widest points along the length of the repeating unit,
wherein the edge to edge distance between a parallel set of
repeating units is equidistant, or roughly equidistant.
20. The method of claim 14, wherein the array of electrodes
comprises a passivation layer with a relative electrical
permittivity from about 2.0 to about 4.0.
21. The method of claim 14, wherein the fluid is a bodily fluid, an
environmental sample, food or beverage, growth medium or water.
Description
CROSS-REFERENCE
[0001] This application is a continuation of U.S. application Ser.
No. 14/067,841, filed Oct. 30, 2013, which is a continuation of
U.S. application Ser. No. 13/864,179, filed Apr. 16, 2013, which
claims the benefit of U.S. Provisional Application No. 61/624,897,
filed Apr. 16, 2012, which application is incorporated herein by
reference.
BACKGROUND OF THE INVENTION
[0002] Exponentially rapid progress has been made in the field of
DNA sequencing in recent years. Methods such as pyrosequencing, ion
semiconductor sequencing and polony sequencing aim to reduce costs
to a point where sequencing a complete genome becomes routine. This
is expected to transform fields as diverse as medicine, renewable
energy, biosecurity and agriculture to name a few. However,
techniques for isolating DNA suitable for sequencing have not kept
pace and there is a threat that this will become a limitation.
SUMMARY OF THE INVENTION
[0003] In some instances, the present invention fulfills a need for
improved methods of nucleic acid isolation from biological samples.
Particular attributes of certain aspects provided herein include a
total sample preparation time of less than about one hour, with
hands-on time of less than about one minute. In some embodiments,
the present invention can be used to isolate DNA from dilute and/or
complex fluids such as blood or environmental samples. In other
aspects, the present invention can use small amounts of starting
material, achieve highly purified nucleic acids, and is amenable to
multiplexed and high-throughput operation.
[0004] Disclosed herein, in some embodiments, is a method for
isolating a nucleic acid from a fluid comprising cells, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes capable of establishing an AC
electrokinetic field region; b. concentrating a plurality of cells
in a first AC electrokinetic field region, wherein the first AC
eletrokinetic field region is a first dielectrophoretic high field
region and the conductivity of the fluid is less than 500 mS/m; c.
lysing the cells on the array; and d. isolating nucleic acid in a
second AC electrokinetic field region, wherein the second AC
electrokinetic field is a second dielectrophoretic high field
region. In some embodiments, the AC electrokinetic field is
produced using an alternating current having a voltage of 1 volt to
40 volts peak-peak, and/or a frequency of 5 Hz to 5,000,000 Hz and
duty cycles from 5% to 50%. In some embodiments, the conductivity
of the fluid is less than 300 mS/m. In some embodiments, the
electrodes are selectively energized to provide the first
dielectrophoretic high field region and subsequently or
continuously selectively energized to provide the second
dielectrophoretic high field region. In some embodiments, the cells
are lysed using a direct current, a chemical lysing agent, an
enzymatic lysing agent, heat, pressure, sonic energy, or a
combination thereof. In some embodiments, the method further
comprises degradation of residual proteins after cell lysis. In
some embodiments, the cells are lysed using a direct current with a
voltage of 1-500 volts, a pulse frequency of 0.2 to 200 Hz with
duty cycles from 10-50%, and a pulse duration of 0.01 to 10 seconds
applied at least once. In some embodiments, the array of electrodes
is spin-coated with a hydrogel having a thickness between about 0.1
microns and 1 micron. In some embodiments, the hydrogel comprises
two or more layers of a synthetic polymer. In some embodiments, the
hydrogel has a viscosity between about 0.5 cP to about 5 cP prior
to spin-coating. In some embodiments, the hydrogel has a
conductivity between about 0.1 S/m to about 1.0 S/m. In some
embodiments, the isolated nucleic acid comprises less than about
10% non-nucleic acid cellular material or cellular protein by mass.
In some embodiments, the method is completed in less than 10
minutes. In some embodiments, the array of electrodes comprises a
wavy line configuration, wherein the configuration comprises a
repeating unit comprising the shape of a pair of dots connected by
linker, wherein the linker tapers inward toward the midpoint
between the pair of dots, wherein the diameters of the dots are the
widest points along the length of the repeating unit, wherein the
edge to edge distance between a parallel set of repeating units is
equidistant, or roughly equidistant. In some embodiments, the array
of electrodes comprises a passivation layer with a relative
electrical permittivity from about 2.0 to about 4.0.
[0005] In some embodiments, disclosed herein is a method for
isolating a nucleic acid from a fluid comprising cells, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes capable of establishing an AC
electrokinetic field region; b. concentrating a plurality of cells
in a first AC electrokinetic field region, wherein the first AC
electrokinetic field region is a first dielectrophoretic low field
region and the conductivity of the fluid is greater than 300 mS/m;
c. isolating nucleic acid in a second AC electrokinetic field
region, wherein the second AC electrokinetic field is a second
eletrophoretic high field region; and d. flushing cells away from
the array. In some embodiments, the AC electrokinetic field is
produced using an alternating current having a voltage of 1 volt to
40 volts peak-peak, and/or a frequency of 5 Hz to 5,000,000 Hz and
duty cycles from 5% to 50%. In some embodiments, the conductivity
of the fluid is greater than 500 mS/m. In some embodiments, the
electrodes are selectively energized to provide the first
dielectrophoretic high field region and subsequently or
continuously selectively energized to provide the second
dielectrophoretic high field region. In some embodiments, the
method further comprises degrading residual proteins on the array.
In some embodiments, the residual proteins are degraded by one or
more of a chemical degradant or an enzymatic degradant. In some
embodiments, the residual proteins are degraded by Proteinase K. In
some embodiments, the array of electrodes is spin-coated with a
hydrogel having a thickness between about 0.1 microns and 1 micron.
In some embodiments, the hydrogel comprises two or more layers of a
synthetic polymer. In some embodiments, the hydrogel has a
viscosity between about 0.5 cP to about 5 cP prior to spin-coating.
In some embodiments, the hydrogel has a conductivity between about
0.1 S/m to about 1.0 S/m. In some embodiments, the isolated nucleic
acid comprises less than about 10% non-nucleic acid cellular
material or cellular protein by mass. In some embodiments, the
method is completed in less than 10 minutes. In some embodiments,
the array of electrodes comprises a wavy line configuration,
wherein the configuration comprises a repeating unit comprising the
shape of a pair of dots connected by linker, wherein the linker
tapers inward toward the midpoint between the pair of dots, wherein
the diameters of the dots are the widest points along the length of
the repeating unit, wherein the edge to edge distance between a
parallel set of repeating units is equidistant, or roughly
equidistant. In some embodiments, the array of electrodes comprises
a passivation layer with a relative electrical permittivity from
about 2.0 to about 4.0.
[0006] Disclosed herein, in some embodiments, is a method for
isolating a nucleic acid from a fluid comprising cells, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes capable of generating an AC
electrokinetic field; b. concentrating a plurality of cells in a
first AC electrokinetic field region; c. lysing the cells in the
first AC electrokinetic field region; and d. isolating the nucleic
acid in a second AC electrokinetic field region, wherein the fluid
is at a conductivity capable of concentrating a plurality of cells
in the first AC electrokinetic field region. In some embodiments,
the first AC electrokinetic region is a dielectrophoretic field
region, wherein the second AC electrokinetic field region is a
dielectrophoretic field region, or a combination thereof. In some
embodiments, the first AC electrokinetic field region is a first
dielectrophoretic low field region and the second AC electrokinetic
field region is a second dielectrophoretic high field region,
wherein the conductivity of the fluid is greater than 300 mS/m. In
some embodiments, the first AC electrokinetic field region is a
first dielectrophoretic high field region and the second AC
electrokinetic field region is a second dielectrophoretic high
field region, wherein the conductivity of the fluid is less than
300 mS/m. In some embodiments, the nucleic acid is concentrated in
the second AC electrokinetic field region. In some embodiments, the
method further comprises flushing residual material from the array
and the isolated nucleic acid. In some embodiments, the method
further comprises degradation of a residual protein. In some
embodiments, the method further comprises flushing degraded
proteins from the array and the isolated nucleic acid. In some
embodiments, the method further comprises collecting the nucleic
acid. In some embodiments, the first AC electrokinetic field region
is produced by an alternating current. In some embodiments, the
first AC electrokinetic field region is produced using an
alternating current having a voltage of 1 volt to 40 volts
peak-peak; and/or a frequency of 5 Hz to 5,000,000 Hz, and duty
cycles from 5% to 50%. In some embodiments, the second AC
electrokinetic field region is a different region of the electrode
array as the first AC electrokinetic field region. In some
embodiments, the second AC electrokinetic field region is the same
region of the electrode array as the first AC electrokinetic field
region. In some embodiments, the second AC electrokinetic field
region is produced by an alternating current. In some embodiments,
the second AC electrokinetic field region is produced using an
alternating current having a voltage of 1 volt to 50 volts
peak-peak; and/or a frequency of 5 Hz to 5,000,000 Hz, and duty
cycles from 5% to 50%. In some embodiments, the electrodes are
selectively energized to provide the first AC electrokinetic field
region and subsequently or continuously selectively energized to
provide the second AC electrokinetic field region. In some
embodiments, the cells are lysed by applying a direct current to
the cells. In some embodiments, the direct current used to lyse the
cells has a voltage of 1-500 volts; and a duration of 0.01 to 10
seconds applied once or as multiple pulses. In some embodiments,
the direct current used to lyse the cells is a direct current pulse
or a plurality of direct current pulses applied at a frequency
suitable for lysing the cells. In some embodiments, the pulse has a
frequency of 0.2 to 200 Hz with duty cycles from 10-50%. In some
embodiments, the cells are lysed on the device using a direct
current, a chemical lysing agent, an enzymatic lysing agent, heat,
osmotic pressure, sonic energy, or a combination thereof. In some
embodiments, the residual material comprises lysed cellular
material. In some embodiments, the lysed cellular material
comprises residual protein freed from the plurality of cells upon
lysis. In some embodiments, the array of electrodes is coated with
a hydrogel. In some embodiments, the hydrogel comprises two or more
layers of a synthetic polymer. In some embodiments, the hydrogel is
spin-coated onto the electrodes. In some embodiments, the hydrogel
has a viscosity between about 0.5 cP to about 5 cP prior to
spin-coating. In some embodiments, the hydrogel has a thickness
between about 0.1 microns and 1 micron. In some embodiments, the
hydrogel has a conductivity between about 0.1 S/m to about 1.0 S/m.
In some embodiments, the array of electrodes is in a dot
configuration. In some embodiments, the angle of orientation
between dots is from about 25.degree. to about 60.degree.. In some
embodiments, the array of electrodes is in a wavy or nonlinear line
configuration, wherein the configuration comprises a repeating unit
comprising the shape of a pair of dots connected by a linker,
wherein the dots and linker define the boundaries of the electrode,
wherein the linker tapers inward towards or at the midpoint between
the pair of dots, wherein the diameters of the dots are the widest
points along the length of the repeating unit, wherein the edge to
edge distance between a parallel set of repeating units is
equidistant, or roughly equidistant. In some embodiments, the array
of electrodes comprises a passivation layer with a relative
electrical permittivity from about 2.0 to about 4.0. In some
embodiments, the method further comprises amplifying the isolated
nucleic acid by polymerase chain reaction. In some embodiments, the
nucleic acid comprises DNA, RNA, or any combination thereof. In
some embodiments, the isolated nucleic acid comprises less than
about 80%, less than about 70%, less than about 60%, less than
about 50%, less than about 40%, less than about 30%, less than
about 20%, less than about 10%, less than about 5%, or less than
about 2% non-nucleic acid cellular material and/or protein by mass.
In some embodiments, the isolated nucleic acid comprises greater
than about 99%, greater than about 98%, greater than about 95%,
greater than about 90%, greater than about 80%, greater than about
70%, greater than about 60%, greater than about 50%, greater than
about 40%, greater than about 30%, greater than about 20%, or
greater than about 10% nucleic acid by mass. In some embodiments,
the method is completed in less than about one hour. In some
embodiments, centrifugation is not used. In some embodiments, the
residual proteins are degraded by one or more of chemical
degradation and enzymatic degradation. In some embodiments, the
residual proteins are degraded by Proteinase K. In some
embodiments, the residual proteins are degraded by an enzyme, the
method further comprising inactivating the enzyme following
degradation of the proteins. In some embodiments, the enzyme is
inactivated by heat (e.g., 50 to 95.degree. C. for 5-15 minutes).
In some embodiments, the residual material and the degraded
proteins are flushed in separate or concurrent steps. In some
embodiments, the isolated nucleic acid is collected by (i) turning
off the second AC electrokinetic field region; and (ii) eluting the
nucleic acid from the array in an eluant. In some embodiments,
nucleic acid is isolated in a form suitable for sequencing. In some
embodiments, the nucleic acid is isolated in a fragmented form
suitable for shotgun-sequencing. In some embodiments, the fluid
comprising cells has a low conductivity or a high conductivity. In
some embodiments, the fluid comprises a bodily fluid, blood, serum,
plasma, urine, saliva, a food, a beverage, a growth medium, an
environmental sample, a liquid, water, clonal cells, or a
combination thereof. In some embodiments, the cells comprise clonal
cells, pathogen cells, bacteria cells, viruses, plant cells, animal
cells, insect cells, and/or combinations thereof. In some
embodiments, the method further comprises sequencing the isolated
nucleic acid. In some embodiments, the nucleic acid is sequenced by
Sanger sequencing, pyrosequencing, ion semiconductor sequencing,
polony sequencing, sequencing by ligation, DNA nanoball sequencing,
sequencing by ligation, or single molecule sequencing. In some
embodiments, the method further comprises performing a reaction on
the DNA (e.g., fragmentation, restriction digestion, ligation). In
some embodiments, the reaction occurs on or near the array or in
the device. In some embodiments, the fluid comprising cells
comprises no more than 10,000 cells.
[0007] Disclosed herein, in some embodiments, is a method for
isolating a nucleic acid from a fluid comprising cells, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes capable of generating an AC
electrokinetic field; b. concentrating a plurality of cells in a
first AC electrokinetic (e.g., dielectrophoretic) field region; c.
isolating nucleic acid in a second AC electrokinetic (e.g.,
dielectrophoretic) field region; and d. flushing cells away,
wherein the fluid is at a conductivity capable of concentrating a
plurality of cells in the first AC electrokinetic field region. In
some embodiments, the first AC electrokinetic field region is a
dielectrophoretic field region. In some embodiments, the first AC
electrokinetic field region is a dielectrophoretic low field
region, and wherein the fluid conductivity is greater than 300
mS/m. In some embodiments, the second AC electrokinetic field
region is a dielectrophoretic field region. In some embodiments,
the method further comprises degradation of residual proteins after
step (e). In some embodiments, the method further comprises
flushing the degraded proteins from the nucleic acid. In some
embodiments, the method further comprises collecting the nucleic
acid. In some embodiments, the first AC electrokinetic field region
is produced by an alternating current. In some embodiments, the
first AC electrokinetic field region is produced using an
alternating current having a voltage of 1 volt to 40 volts
peak-peak; and/or a frequency of 5 Hz to 5,000,000 Hz, and duty
cycles from 5% to 50%. In some embodiments, the second AC
electrokinetic field region is a different region of the electrode
array as the first AC electrokinetic field region. In some
embodiments, the second AC electrokinetic field region is the same
region of the electrode array as the first AC electrokinetic field
region. In some embodiments, the second AC electrokinetic field
region is produced by an alternating current. In some embodiments,
the second AC electrokinetic field region is a dielectrophoretic
high field region. In some embodiments, the second AC
electrokinetic field region is produced using an alternating
current having a voltage of 1 volt to 50 volts peak-peak; and/or a
frequency of 5 Hz to 5,000,000 Hz, and duty cycles from 5% to 50%.
In some embodiments, the electrodes are selectively energized to
provide the first AC electrokinetic field region and subsequently
or continuously selectively energized to provide the second AC
electrokinetic field region. In some embodiments, the array of
electrodes is coated with a hydrogel. In some embodiments, the
hydrogel comprises two or more layers of a synthetic polymer. In
some embodiments, the hydrogel is spin-coated onto the electrodes.
In some embodiments, the hydrogel has a viscosity between about 0.5
cP to about 5 cP prior to spin-coating. In some embodiments, the
hydrogel has a thickness between about 0.1 microns and 1 micron. In
some embodiments, the hydrogel has a conductivity between about 0.1
S/m to about 1.0 S/m. In some embodiments, the array of electrodes
is in a dot configuration. In some embodiments, the angle of
orientation between dots is from about 25.degree. to about
60.degree.. In some embodiments, the array of electrodes is in a
wavy or nonlinear line configuration, wherein the configuration
comprises a repeating unit comprising the shape of a pair of dots
connected by a linker, wherein the dots and linker define the
boundaries of the electrode, wherein the linker tapers inward
towards or at the midpoint between the pair of dots, wherein the
diameters of the dots are the widest points along the length of the
repeating unit, wherein the edge to edge distance between a
parallel set of repeating units is equidistant, or roughly
equidistant. In some embodiments, the array of electrodes comprises
a passivation layer with a relative electrical permittivity from
about 2.0 to about 4.0. In some embodiments, the method further
comprises amplifying the isolated nucleic acid by polymerase chain
reaction. In some embodiments, the nucleic acid comprises DNA, RNA,
or any combination thereof. In some embodiments, the isolated
nucleic acid comprises less than about 80%, less than about 70%,
less than about 60%, less than about 50%, less than about 40%, less
than about 30%, less than about 20%, less than about 10%, less than
about 5%, or less than about 2% non-nucleic acid cellular material
and/or protein by mass. In some embodiments, the isolated nucleic
acid comprises greater than about 99%, greater than about 98%,
greater than about 95%, greater than about 90%, greater than about
80%, greater than about 70%, greater than about 60%, greater than
about 50%, greater than about 40%, greater than about 30%, greater
than about 20%, or greater than about 10% nucleic acid by mass. In
some embodiments, the method is completed in less than about one
hour. In some embodiments, centrifugation is not used. In some
embodiments, the residual proteins are degraded by one or more of
chemical degradation and enzymatic degradation. In some
embodiments, the residual proteins are degraded by Proteinase K. In
some embodiments, the residual proteins are degraded by an enzyme,
the method further comprising inactivating the enzyme following
degradation of the proteins. In some embodiments, the enzyme is
inactivated by heat (e.g., 50 to 95.degree. C. for 5-15 minutes).
In some embodiments, the residual material and the degraded
proteins are flushed in separate or concurrent steps. In some
embodiments, the isolated nucleic acid is collected by (i) turning
off the second AC electrokinetic field region; and (ii) eluting the
nucleic acid from the array in an eluant. In some embodiments,
nucleic acid is isolated in a form suitable for sequencing. In some
embodiments, the nucleic acid is isolated in a fragmented form
suitable for shotgun-sequencing. In some embodiments, the fluid
comprising cells has a low conductivity or a high conductivity. In
some embodiments, the fluid comprises a bodily fluid, blood, serum,
plasma, urine, saliva, a food, a beverage, a growth medium, an
environmental sample, a liquid, water, clonal cells, or a
combination thereof. In some embodiments, the cells comprise clonal
cells, pathogen cells, bacteria cells, viruses, plant cells, animal
cells, insect cells, and/or combinations thereof. In some
embodiments, the method further comprises sequencing the isolated
nucleic acid. In some embodiments, the nucleic acid is sequenced by
Sanger sequencing, pyrosequencing, ion semiconductor sequencing,
polony sequencing, sequencing by ligation, DNA nanoball sequencing,
sequencing by ligation, or single molecule sequencing. In some
embodiments, the method further comprises performing a reaction on
the DNA (e.g., fragmentation, restriction digestion, ligation). In
some embodiments, the reaction occurs on or near the array or in
the device. In some embodiments, the fluid comprising cells
comprises no more than 10,000 cells.
[0008] In some embodiments, disclosed herein is a device for
isolating a nucleic acid from a fluid comprising cells, the device
comprising: a. a housing; b. a heater and/or a reservoir comprising
a protein degradation agent; and c. a plurality of alternating
current (AC) electrodes within the housing, the AC electrodes
configured to be selectively energized to establish AC
electrokinetic high field and AC electrokinetic low field regions,
whereby AC electrokinetic effects provide for concentration of
cells in low field regions of the device. In some embodiments, the
plurality of electrodes is configured to be selectively energized
to establish a dielectrophoretic high field and dielectrophoretic
low field regions. In some embodiments, the array of electrodes is
coated with a hydrogel. In some embodiments, the hydrogel comprises
two or more layers of a synthetic polymer. In some embodiments, the
hydrogel is spin-coated onto the electrodes. In some embodiments,
the hydrogel has a viscosity between about 0.5 cP to about 5 cP
prior to spin-coating. In some embodiments, the hydrogel has a
thickness between about 0.1 microns and 1 micron. In some
embodiments, the hydrogel has a conductivity between about 0.1 S/m
to about 1.0 S/m. In some embodiments, the array of electrodes is
in a dot configuration. In some embodiments, the angle of
orientation between dots is from about 25.degree. to about
60.degree.. In some embodiments, the array of electrodes is in a
wavy or nonlinear line configuration, wherein the configuration
comprises a repeating unit comprising the shape of a pair of dots
connected by a linker, wherein the dots and linker define the
boundaries of the electrode, wherein the linker tapers inward
towards or at the midpoint between the pair of dots, wherein the
diameters of the dots are the widest points along the length of the
repeating unit, wherein the edge to edge distance between a
parallel set of repeating units is equidistant, or roughly
equidistant. In some embodiments, the array of electrodes comprises
a passivation layer with a relative electrical permittivity from
about 2.0 to about 4.0. In some embodiments, the protein
degradation agent is Proteinase K. In some embodiments, the device
further comprises a second reservoir comprising an eluant.
[0009] In some embodiments, disclosed herein is a system for
isolating a nucleic acid from a fluid comprising cells, the system
comprising: a. a device comprising a plurality of alternating
current (AC) electrodes, the AC electrodes configured to be
selectively energized to establish AC electrokinetic high field and
AC electrokinetic low field regions, whereby AC electrokinetic
effects provide for concentration of cells in high field regions of
the device, wherein the configuration comprises a repeating unit
comprising the shape of a pair of dots connected by a linker,
wherein the dots and linker define the boundaries of the electrode,
wherein the linker tapers inward towards or at the midpoint between
the pair of dots, wherein the diameters of the dots are the widest
points along the length of the repeating unit, wherein the edge to
edge distance between a parallel set of repeating units is
equidistant, or roughly equidistant; and b. a module capable of
sequencing DNA by Sanger sequencing or next generation sequencing
methods; c. a software program capable of controlling the device
comprising a plurality of AC electrodes, the module capable of
sequencing DNA or a combination thereof; and d. a fluid comprising
cells. In some embodiments, the plurality of electrodes is
configured to be selectively energized to establish a
dielectrophoretic high field and dielectrophoretic low field
regions.
[0010] Disclosed herein, in some embodiments, is a device
comprising: a. a plurality of alternating current (AC) electrodes,
the AC electrodes configured to be selectively energized to
establish AC electrokinetic high field and AC electrokinetic low
field regions, wherein the array of electrodes is in a wavy or
nonlinear line configuration, wherein the configuration comprises a
repeating unit comprising the shape of a pair of dots connected by
a linker, wherein the dots and linker define the boundaries of the
electrode, wherein the linker tapers inward towards or at the
midpoint between the pair of dots, wherein the diameters of the
dots are the widest points along the length of the repeating unit,
wherein the edge to edge distance between a parallel set of
repeating units is equidistant, or roughly equidistant; and b. a
module capable of thermocycling and amplifying nucleic acids. In
some embodiments, the plurality of electrodes is configured to be
selectively energized to establish a dielectrophoretic high field
and dielectrophoretic low field regions. In some embodiments, the
device is capable of isolating nucleic acids from a fluid
comprising cells and performing amplification of the isolated
nucleic acids. In some embodiments, the isolated nucleic acid is
DNA or mRNA. In some embodiments, nucleic acid is isolated and
amplification is performed in a single chamber. In some
embodiments, nucleic acid is isolated and amplification is
performed in multiple regions of a single chamber. In some
embodiments, the device further comprises using at least one of an
elution tube, a chamber and a reservoir to perform amplification.
In some embodiments, amplification of the nucleic acid is
polymerase chain reaction (PCR)-based. In some embodiments,
amplification of the nucleic acid is performed in a serpentine
microchannel comprising a plurality of temperature zones. In some
embodiments, amplification is performed in aqueous droplets
entrapped in immiscible fluids (i.e., digital PCR). In some
embodiments, the thermocycling comprises convection. In some
embodiments, the device comprises a surface contacting or proximal
to the electrodes, wherein the surface is functionalized with
biological ligands that are capable of selectively capturing
biomolecules. In some embodiments, the array of electrodes is
coated with a hydrogel. In some embodiments, the hydrogel comprises
two or more layers of a synthetic polymer. In some embodiments, the
hydrogel is spin-coated onto the electrodes. In some embodiments,
the hydrogel has a viscosity between about 0.5 cP to about 5 cP
prior to spin-coating. In some embodiments, the hydrogel has a
thickness between about 0.1 microns and 1 micron. In some
embodiments, the hydrogel has a conductivity between about 0.1 S/m
to about 1.0 S/m. In some embodiments, the array of electrodes
comprises a passivation layer with a relative electrical
permittivity from about 2.0 to about 4.0. In some embodiments, the
surface selectively captures biomolecules by: a. nucleic acid
hybridization; b. antibody--antigen interactions; c. biotin--avidin
interactions; d. ionic or electrostatic interactions; or e. any
combination thereof. In some embodiments, the surface is
functionalized to minimize and/or inhibit nonspecific binding
interactions by: a. polymers (e.g., polyethylene glycol PEG); b.
ionic or electrostatic interactions; c.
[0011] surfactants; or d. any combination thereof. In some
embodiments, the device comprises a plurality of microelectrode
devices oriented (a) flat side by side, (b) facing vertically, or
(c) facing horizontally. In some embodiments, the device comprises
a module capable of performing Sanger sequencing. In some
embodiments, the module capable of performing Sanger sequencing
comprises a module capable of capillary electrophoresis, a module
capable of multi-color fluorescence detection, or a combination
thereof.
[0012] Disclosed herein, in some embodiments, is a device
comprising: a. a plurality of alternating current (AC) electrodes,
the AC electrodes configured to be selectively energized to
establish AC electrokinetic high field and AC electrokinetic low
field regions, wherein the array of electrodes is in a wavy or
nonlinear line configuration, wherein the configuration comprises a
repeating unit comprising the shape of a pair of dots connected by
a linker, wherein the dots and linker define the boundaries of the
electrode, wherein the linker tapers inward towards or at the
midpoint between the pair of dots, wherein the diameters of the
dots are the widest points along the length of the repeating unit,
wherein the edge to edge distance between a parallel set of
repeating units is equidistant, or roughly equidistant; and b. a
module capable of performing sequencing. In some embodiments, the
plurality of electrodes is configured to be selectively energized
to establish a dielectrophoretic high field and dielectrophoretic
low field regions. In some embodiments, the device comprises a
surface contacting or proximal to the electrodes, wherein the
surface is functionalized with biological ligands that are capable
of selectively capturing biomolecules. In some embodiments, the
array of electrodes is coated with a hydrogel. In some embodiments,
the hydrogel comprises two or more layers of a synthetic polymer.
In some embodiments, the hydrogel is spin-coated onto the
electrodes. In some embodiments, the hydrogel has a viscosity
between about 0.5 cP to about 5 cP prior to spin-coating. In some
embodiments, the hydrogel has a thickness between about 0.1 microns
and 1 micron. In some embodiments, the hydrogel has a conductivity
between about 0.1 S/m to about 1.0 S/m. In some embodiments, the
array of electrodes comprises a passivation layer with a relative
electrical permittivity from about 2.0 to about 4.0. In some
embodiments, the surface selectively captures biomolecules by: a.
nucleic acid hybridization; b. antibody--antigen interactions; c.
biotin--avidin interactions; d. ionic or electrostatic
interactions; or e. any combination thereof. In some embodiments,
the surface is functionalized to minimize and/or inhibit
nonspecific binding interactions by: a. polymers (e.g.,
polyethylene glycol PEG); b. ionic or electrostatic interactions;
c. surfactants; or d. any combination thereof. In some embodiments,
the device comprises a plurality of microelectrode devices oriented
(a) flat side by side, (b) facing vertically, or (c) facing
horizontally. In some embodiments, the device comprises a module
capable of performing next generation sequencing. In some
embodiments, the module capable of performing next-generation
sequencing is capable of performing pyrosequencing, ion
semiconductor sequencing, polony sequencing, sequencing by
ligation, DNA nanoball sequencing, or single molecule
sequencing.
[0013] Disclosed herein, in some embodiments, is a method of
isolating a nucleic acid from a fluid comprising cells, comprising
a) performing a method disclosed herein; b) performing PCR
amplification on the nucleic acid, or a cDNA version of the nucleic
acid, to produce a PCR product; c) isolating the PCR product in a
third AC electrokinetic region; d) performing Sanger chain
termination reactions on the PCR product to produce a sequencing
product of the nucleic acid; and e) performing electrophoretic
separation of the sequencing product of the nucleic acid. In some
embodiments, the third AC electrokinetic region is a
dielectrophoretic field region. In some embodiments, the third AC
electrokinetic region is a dielectrophoretic high field region. In
some embodiments, the array of electrodes is in a wavy or nonlinear
line configuration, wherein the configuration comprises a repeating
unit comprising the shape of a pair of dots connected by a linker,
wherein the dots and linker define the boundaries of the electrode,
wherein the linker tapers inward towards or at the midpoint between
the pair of dots, wherein the diameters of the dots are the widest
points along the length of the repeating unit, wherein the edge to
edge distance between a parallel set of repeating units is
equidistant, or roughly equidistant. In some embodiments, the
electrophoretic separation of the sequencing product of the nucleic
acid is capillary electrophoresis. In some embodiments, the method
further comprises the use of multicolor fluorescence detection to
analyze the sequencing product of the nucleic acid. In some
embodiments, all steps are performed on a single chip. In some
embodiments, the fluid comprising cells comprises no more than
10,000 cells.
INCORPORATION BY REFERENCE
[0014] All publications, patents, and patent applications mentioned
in this specification are herein incorporated by reference to the
same extent as if each individual publication, patent, or patent
application was specifically and individually indicated to be
incorporated by reference.
BRIEF DESCRIPTION OF THE DRAWINGS
[0015] The novel features of the invention are set forth with
particularity in the appended claims. A better understanding of the
features and advantages of the present invention will be obtained
by reference to the following detailed description that sets forth
illustrative embodiments, in which the principles of the invention
are utilized, and the accompanying drawings of which:
[0016] FIG. 1 shows a top view (A), a bottom view (B) and a
cross-sectional view (C) of an exemplary device.
[0017] FIG. 2 shows the electrodes associated with various amounts
of genomic DNA.
[0018] FIG. 3 shows isolation of green fluorescent E. coli on an
array. Panel (A) shows a bright field view. Panel (B) shows a green
fluorescent view of the electrodes before DEP activation. Panel (C)
shows E. coli on the electrodes after one minute at 10 kHz, 20 Vp-p
in 1.times.TBE buffer. Panel (D) shows E. coli on the electrodes
after one minute at 1 MHz, 20 Vp-p in 1.times.TBE buffer.
[0019] FIG. 4 shows a comparison between the methods of the present
invention (top right panel) and the Epicentre.TM. WaterMaster.TM.
DNA purification procedure (top left panel). The pie charts are the
distribution of 10,000 Illumina.TM. sequencing reads BLAST searched
against the MEGAN.TM. database. As shown, a similar percentage of
sequencing reads originated from E. coli sequence for both methods.
The table in the lower panel shows Sequencing coverage and quality
of E. Coli run through the chip and compared to a control run
outside the chip according to manufacturer's protocol.
[0020] FIG. 5 shows an exemplary method for isolating nucleic acids
from cells.
[0021] FIG. 6 shows an exemplary method for isolating
extra-cellular nucleic acids from a fluid comprising cells.
[0022] FIG. 7 exemplifies ACEK (AC Electrokinetic) forces that
result due to the methods and devices disclosed herein. Using the
relationship between forces on particles due to Dielectrophoresis
(DEP), AC Electrothermal (ACET) flow and AC Electroosmosis, (ACEO),
in some embodiments, size cut-offs are used for nucleic acid
isolation and purification. Isolation relies on flow vortices that
will brings nucleic acids closer to an electrode edge due to ACET
and ACEO depending on fluid conductivity, A DEP trap holds onto
particles once they are at the trap site, depending on the
effective Stokes radius.
[0023] FIG. 8 exemplifies a wavy electrode configuration, as
disclosed herein. The edge to edge distance between electrodes is
generally equidistant throughout. A wavy electrode configuration
maximizes electrode surface area while maintaining alternating
non-uniform electric field to induce ACEK gradient to enable DEP,
ACEO, ACET, and other ACEK forces.
[0024] FIG. 9 exemplifies how the E-field gradient at a dielectric
layer corner based on silicon nitride thickness. Lower K and lower
thickness resulted in higher E-field gradient (bending) at a
dielectric layer corner.
[0025] FIG. 10 exemplifies DNA capture on an electrode with a vapor
deposited hydrogel layer. Vapor phase coatings of activated
monomers form uniform thin film coatings on a variety of
substrates. Hydrogels such as pHEMA were deposited in various
thickness (100, 200, 300, 400 nm) and crosslinking (5, 25, 40%)
density on electrode chips by GVD Corporation (Cambridge, Mass.).
The hydrogel films were tested using a standard ACE protocol (no
pretreatment, 7Vp-p, 10 KHz, 2 minutes, 0.5.times.PBS, 500 ng/ml
gDNA labeled with Sybr Green 1). Fluorescence on the electrodes was
captured by imaging. The 100 nm thickness, 5% crosslink gel device
was found to have strong DNA capture. Optionally, the process could
be optimized by changing the deposition rate or anchoring growth to
the surface of the microelectrode array (i.e., to the passivation
layer and exposed electrodes), using an adhesion promote such as a
silane derivative.
DETAILED DESCRIPTION OF THE INVENTION
[0026] Described herein are methods, devices and systems suitable
for isolating or separating particles or molecules from a fluid
composition. In specific embodiments, provided herein are methods,
devices and systems for isolating or separating a nucleic acid from
a fluid comprising cells or other particulate material. In some
aspects, the methods, devices and systems may allow for rapid
separation of particles and molecules in a fluid composition. In
other aspects, the methods, devices and systems may allow for rapid
isolation of molecules from particles in a fluid composition. In
various aspects, the methods, devices and systems may allow for a
rapid procedure that requires a minimal amount of material and/or
results in high purity DNA isolated from complex fluids such as
blood or environmental samples.
[0027] Provided in certain embodiments herein are methods, devices
and systems for isolating or separating particles or molecules from
a fluid composition, the methods, devices, and systems comprising
applying the fluid to a device comprising an array of electrodes
and being capable of generating AC electrokinetic forces (e.g.,
when the array of electrodes are energized). In some embodiments,
the dielectrophoretic field, is a component of AC electrokinetic
force effects. In other embodiments, the component of AC
electrokinetic force effects is AC electroosmosis or AC
electrothermal effects. In some embodiments the AC electrokinetic
force, including dielectrophoretic fields, comprises high-field
regions (positive DEP, i.e. area where there is a strong
concentration of electric field lines due to a non-uniform electric
field) and/or low-field regions (negative DEP, i.e. area where
there is a weak concentration of electric field lines due to a
non-uniform electric field).
[0028] In specific instances, the particles or molecules (e.g.,
nucleic acid) are isolated (e.g., isolated or separated from cells)
in a field region (e.g., a high field region) of the
dielectrophoretic field. In some embodiments, the method, device,
or system further includes one or more of the following steps:
concentrating cells of interest in a first dielectrophoretic field
region (e.g., a high field DEP region), lysing cells in the first
dielectrophoretic field region, and/or concentrating nucleic acid
in a first or second dielectrophoretic field region. In other
embodiments, the method, device, or system includes one or more of
the following steps: concentrating cells in a first
dielectrophoretic field region (e.g., a low field DEP region),
concentrating nucleic acid in a second dielectrophoretic field
region (e.g., a high field DEP region), and washing away the cells
and residual material. The method also optionally includes devices
and/or systems capable of performing one or more of the following
steps: washing or otherwise removing residual (e.g., cellular)
material from the nucleic acid (e.g., rinsing the array with water
or buffer while the nucleic acid is concentrated and maintained
within a high field DEP region of the array), degrading residual
proteins (e.g., residual proteins from lysed cells and/or other
sources, such degradation occurring according to any suitable
mechanism, such as with heat, a protease, or a chemical), flushing
degraded proteins from the nucleic acid, and collecting the nucleic
acid. In some embodiments, the result of the methods, operation of
the devices, and operation of the systems described herein is an
isolated nucleic acid, optionally of suitable quantity and purity
for DNA sequencing.
[0029] In some instances, it is advantageous that the methods
described herein are performed in a short amount of time, the
devices are operated in a short amount of time, and the systems are
operated in a short amount of time. In some embodiments, the period
of time is short with reference to the "procedure time" measured
from the time between adding the fluid to the device and obtaining
isolated nucleic acid. In some embodiments, the procedure time is
less than 3 hours, less than 2 hours, less than 1 hour, less than
30 minutes, less than 20 minutes, less than 10 minutes, or less
than 5 minutes.
[0030] In another aspect, the period of time is short with
reference to the "hands-on time" measured as the cumulative amount
of time that a person must attend to the procedure from the time
between adding the fluid to the device and obtaining isolated
nucleic acid. In some embodiments, the hands-on time is less than
20 minutes, less than 10 minutes, less than 5 minute, less than 1
minute, or less than 30 seconds.
[0031] In some instances, it is advantageous that the devices
described herein comprise a single vessel, the systems described
herein comprise a device comprising a single vessel and the methods
described herein can be performed in a single vessel, e.g., in a
dielectrophoretic device as described herein. In some aspects, such
a single-vessel embodiment minimizes the number of fluid handling
steps and/or is performed in a short amount of time. In some
instances, the present methods, devices and systems are contrasted
with methods, devices and systems that use one or more
centrifugation steps and/or medium exchanges. In some instances,
centrifugation increases the amount of hands-on time required to
isolate nucleic acids. In another aspect, the single-vessel
procedure or device isolates nucleic acids using a minimal amount
of consumable reagents.
Devices and Systems
[0032] In some embodiments, described herein are devices for
collecting a nucleic acid from a fluid. In one aspect, described
herein are devices for collecting a nucleic acid from a fluid
comprising cells or other particulate material. In other aspects,
the devices disclosed herein are capable of collecting and/or
isolating nucleic acid from a fluid comprising cellular or protein
material. In other instances, the devices disclosed herein are
capable of collecting and/or isolating nucleic acid from cellular
material.
[0033] In some embodiments, disclosed herein is a device for
isolating a nucleic acid from a fluid comprising cells or other
particulate material, the device comprising: a. a housing; b. a
heater or thermal source and/or a reservoir comprising a protein
degradation agent; and c. a plurality of alternating current (AC)
electrodes within the housing, the AC electrodes configured to be
selectively energized to establish AC electrokinetic high field and
AC electrokinetic low field regions, whereby AC electrokinetic
effects provide for concentration of cells in low field regions of
the device. In some embodiments, the plurality of electrodes is
configured to be selectively energized to establish a
dielectrophoretic high field and dielectrophoretic low field
regions. In some embodiments, the protein degradation agent is a
protease. In some embodiments, the protein degradation agent is
Proteinase K. In some embodiments, the device further comprises a
second reservoir comprising an eluant.
[0034] In some embodiments, disclosed herein is a device
comprising: a. a plurality of alternating current (AC) electrodes,
the AC electrodes configured to be selectively energized to
establish AC electrokinetic high field and AC electrokinetic low
field regions; and b. a module capable of thermocycling and
performing PCR or other enzymatic reactions. In some embodiments,
the plurality of electrodes is configured to be selectively
energized to establish a dielectrophoretic high field and
dielectrophoretic low field regions. In some embodiments, the
device is capable of isolating DNA from a fluid comprising cells
and performing PCR amplification or other enzymatic reactions. In
some embodiments, DNA is isolated and PCR or other enzymatic
reaction is performed in a single chamber. In some embodiments, DNA
is isolated and PCR or other enzymatic reaction is performed in
multiple regions of a single chamber. In some embodiments, DNA is
isolated and PCR or other enzymatic reaction is performed in
multiple chambers.
[0035] In some embodiments, the device further comprises at least
one of an elution tube, a chamber and a reservoir to perform PCR
amplification or other enzymatic reaction. In some embodiments, PCR
amplification or other enzymatic reaction is performed in a
serpentine microchannel comprising a plurality of temperature
zones. In some embodiments, PCR amplification or other enzymatic
reaction is performed in aqueous droplets entrapped in immiscible
fluids (i.e., digital PCR). In some embodiments, the thermocycling
comprises convection. In some embodiments, the device comprises a
surface contacting or proximal to the electrodes, wherein the
surface is functionalized with biological ligands that are capable
of selectively capturing biomolecules.
[0036] In some embodiments, disclosed herein is a system for
isolating a nucleic acid from a fluid comprising cells or other
particulate material, the system comprising: a. a device comprising
a plurality of alternating current (AC) electrodes, the AC
electrodes configured to be selectively energized to establish AC
electrokinetic high field and AC electrokinetic low field regions,
whereby AC electrokinetic effects provide for concentration of
cells in high field regions of the device; and b. a sequencer,
thermocycler or other device for performing enzymatic reactions on
isolated or collected nucleic acid. In some embodiments, the
plurality of electrodes is configured to be selectively energized
to establish a dielectrophoretic high field and dielectrophoretic
low field regions.
[0037] In various embodiments, DEP fields are created or capable of
being created by selectively energizing an array of electrodes as
described herein. The electrodes are optionally made of any
suitable material resistant to corrosion, including metals, such as
noble metals (e.g. platinum, platinum iridium alloy, palladium,
gold, and the like). In various embodiments, electrodes are of any
suitable size, of any suitable orientation, of any suitable
spacing, energized or capable of being energized in any suitable
manner, and the like such that suitable DEP and/or other
electrokinetic fields are produced.
[0038] In some embodiments described herein are methods, devices
and systems in which the electrodes are placed into separate
chambers and positive DEP regions and negative DEP regions are
created within an inner chamber by passage of the AC DEP field
through pore or hole structures. Various geometries are used to
form the desired positive DEP (high field) regions and DEP negative
(low field) regions for carrying cellular, microparticle,
nanoparticle, and nucleic acid separations. In some embodiments,
pore or hole structures contain (or are filled with) porous
material (hydrogels) or are covered with porous membrane
structures. In some embodiments, by segregating the electrodes into
separate chambers, such pore/hole structure DEP devices reduce
electrochemistry effects, heating, or chaotic fluidic movement from
occurring in the inner separation chamber during the DEP
process.
[0039] In one aspect, described herein is a device comprising
electrodes, wherein the electrodes are placed into separate
chambers and DEP fields are created within an inner chamber by
passage through pore structures. The exemplary device includes a
plurality of electrodes and electrode-containing chambers within a
housing. A controller of the device independently controls the
electrodes, as described further in PCT patent publication WO
2009/146143 A2, which is incorporated herein for such
disclosure.
[0040] In some embodiments, chambered devices are created with a
variety of pore and/or hole structures (nanoscale, microscale and
even macroscale) and contain membranes, gels or filtering materials
which control, confine or prevent cells, nanoparticles or other
entities from diffusing or being transported into the inner
chambers while the AC/DC electric fields, solute molecules, buffer
and other small molecules can pass through the chambers.
[0041] In various embodiments, a variety of configurations for the
devices are possible. For example, a device comprising a larger
array of electrodes, for example in a square or rectangular pattern
configured to create a repeating non-uniform electric field to
enable AC electrokinetics. For illustrative purposes only, a
suitable electrode array may include, but is not limited to, a
10.times.10 electrode configuration, a 50.times.50 electrode
configuration, a 10.times.100 electrode configuration, 20.times.100
electrode configuration, or a 20.times.80 electrode
configuration.
[0042] Such devices include, but are not limited to, multiplexed
electrode and chambered devices, devices that allow reconfigurable
electric field patterns to be created, devices that combine DC
electrophoretic and fluidic processes; sample preparation devices,
sample preparation, enzymatic manipulation of isolated nucleic acid
molecules and diagnostic devices that include subsequent detection
and analysis, lab-on-chip devices, point-of-care and other clinical
diagnostic systems or versions.
[0043] In some embodiments, a planar platinum electrode array
device comprises a housing through which a sample fluid flows. In
some embodiments, fluid flows from an inlet end to an outlet end,
optionally comprising a lateral analyte outlet. The exemplary
device includes multiple AC electrodes. In some embodiments, the
sample consists of a combination of micron-sized entities or cells,
larger nanoparticulates and smaller nanoparticulates or
biomolecules. In some instances, the larger nanoparticulates are
cellular debris dispersed in the sample. In some embodiments, the
smaller nanoparticulates are proteins, smaller DNA, RNA and
cellular fragments. In some embodiments, the planar electrode array
device is a 60.times.20 electrode array that is optionally
sectioned into three 20.times.20 arrays that can be separately
controlled but operated simultaneously. The optional auxiliary DC
electrodes can be switched on to positive charge, while the
optional DC electrodes are switched on to negative charge for
electrophoretic purposes. In some instances, each of the controlled
AC and DC systems is used in both a continuous and/or pulsed manner
(e.g., each can be pulsed on and off at relatively short time
intervals) in various embodiments. The optional planar electrode
arrays along the sides of the sample flow, when over-layered with
nanoporous material (e.g., a hydrogel of synthetic polymer), are
optionally used to generate DC electrophoretic forces as well as AC
DEP. Additionally, microelectrophoretic separation processes is
optionally carried out within the nanopore layers using planar
electrodes in the array and/or auxiliary electrodes in the x-y-z
dimensions.
[0044] In various embodiments these methods, devices and systems
are operated in the AC frequency range of from 1,000 Hz to 100 MHz,
at voltages which could range from approximately 1 volt to 2000
volts pk-pk; at DC voltages from 1 volt to 1000 volts, at flow
rates of from 10 microliters per minute to 10 milliliter per
minute, and in temperature ranges from 1.degree. C. to 120.degree.
C. In some embodiments, the methods, devices and systems are
operated in AC frequency ranges of from about 3 to about 15 kHz. In
some embodiments, the methods, devices, and systems are operated at
voltages of from 5-25 volts pk-pk. In some embodiments, the
methods, devices and systems are operated at voltages of from about
1 to about 50 volts/cm. In some embodiments, the methods, devices
and systems are operated at DC voltages of from about 1 to about 5
volts. In some embodiments, the methods, devices and systems are
operated at a flow rate of from about 10 microliters to about 500
microliters per minute. In some embodiments, the methods, devices
and systems are operated in temperature ranges of from about
20.degree. C. to about 60.degree. C. In some embodiments, the
methods, devices and systems are operated in AC frequency ranges of
from 1,000 Hz to 10 MHz. In some embodiments, the methods, devices
and systems are operated in AC frequency ranges of from 1,000 Hz to
1 MHz. In some embodiments, the methods, devices and systems are
operated in AC frequency ranges of from 1,000 Hz to 100 kHz. In
some embodiments, the methods, devices and systems are operated in
AC frequency ranges of from 1,000 Hz to 10 kHz. In some
embodiments, the methods, devices and systems are operated in AC
frequency ranges of from 10 kHz to 100 kHz. In some embodiments,
the methods, devices and systems are operated in AC frequency
ranges of from 100 kHz to 1 MHz. In some embodiments, the methods,
devices and systems are operated at voltages from approximately 1
volt to 1500 volts pk-pk. In some embodiments, the methods, devices
and systems are operated at voltages from approximately 1 volt to
1500 volts pk-pk. In some embodiments, the methods, devices and
systems are operated at voltages from approximately 1 volt to 1000
volts pk-pk. In some embodiments, the methods, devices and systems
are operated at voltages from approximately 1 volt to 500 volts
pk-pk. In some embodiments, the methods, devices and systems are
operated at voltages from approximately 1 volt to 250 volts pk-pk.
In some embodiments, the methods, devices and systems are operated
at voltages from approximately 1 volt to 100 volts pk-pk. In some
embodiments, the methods, devices and systems are operated at
voltages from approximately 1 volt to 50 volts pk-pk. In some
embodiments, the methods, devices and systems are operated at DC
voltages from 1 volt to 1000 volts. In some embodiments, the
methods, devices and systems are operated at DC voltages from 1
volt to 500 volts. In some embodiments, the methods, devices and
systems are operated at DC voltages from 1 volt to 250 volts. In
some embodiments, the methods, devices and systems are operated at
DC voltages from 1 volt to 100 volts. In some embodiments, the
methods, devices and systems are operated at DC voltages from 1
volt to 50 volts. In some embodiments, the methods, devices, and
systems are operated at flow rates of from 10 microliters per
minute to 1 ml per minute. In some embodiments, the methods,
devices, and systems are operated at flow rates of from 10
microliters per minute to 500 microliters per minute. In some
embodiments, the methods, devices, and systems are operated at flow
rates of from 10 microliters per minute to 250 microliters per
minute. In some embodiments, the methods, devices, and systems are
operated at flow rates of from 10 microliters per minute to 100
microliters per minute. In some embodiments, the methods, devices,
and systems are operated in temperature ranges from 1.degree. C. to
100.degree. C. In some embodiments, the methods, devices, and
systems are operated in temperature ranges from 20.degree. C. to
95.degree. C. In some embodiments, the methods, devices, and
systems are operated in temperature ranges from 25.degree. C. to
100.degree. C. In some embodiments, the methods, devices, and
systems are operated at room temperature.
[0045] In some embodiments, the controller independently controls
each of the electrodes. In some embodiments, the controller is
externally connected to the device such as by a socket and plug
connection, or is integrated with the device housing.
[0046] Also described herein are scaled sectioned (x-y dimensional)
arrays of robust electrodes and strategically placed (x-y-z
dimensional) arrangements of auxiliary electrodes that combine DEP,
electrophoretic, and fluidic forces, and use thereof. In some
embodiments, clinically relevant volumes of blood, serum, plasma,
or other samples are more directly analyzed under higher ionic
strength and/or conductance conditions. Described herein is the
overlaying of robust electrode structures (e.g. platinum,
palladium, gold, etc.) with one or more porous layers of materials
(natural or synthetic porous hydrogels, membranes, controlled
nanopore materials, and thin dielectric layered materials) to
reduce the effects of any electrochemistry (electrolysis)
reactions, heating, and chaotic fluid movement that may occur on or
near the electrodes, and still allow the effective separation of
cells, bacteria, virus, nanoparticles, DNA, and other biomolecules
to be carried out. In some embodiments, in addition to using AC
frequency cross-over points to achieve higher resolution
separations, on-device (on-array) DC microelectrophoresis is used
for secondary separations. For example, the separation of DNA
nanoparticulates (20-50 kb), high molecular weight DNA (5-20 kb),
intermediate molecular weight DNA (1-5 kb), and lower molecular
weight DNA (0.1-1 kb) fragments may be accomplished through DC
microelectrophoresis on the array. In some embodiments, the device
is sub-sectioned, optionally for purposes of concurrent separations
of different blood cells, bacteria and virus, and DNA carried out
simultaneously on such a device.
[0047] In some embodiments, the device comprises a housing and a
heater or thermal source and/or a reservoir comprising a protein
degradation agent. In some embodiments, the heater or thermal
source is capable of increasing the temperature of the fluid to a
desired temperature (e.g., to a temperature suitable for degrading
proteins, about 30.degree. C., 40.degree. C., 50.degree. C.,
60.degree. C., 70.degree. C., or the like). In some embodiments,
the heater or thermal source is suitable for operation as a PCR
thermocycler. IN other embodiments, the heater or thermal source is
used to maintain a constant temperature (isothermal conditions). In
some embodiments, the protein degradation agent is a protease. In
other embodiments, the protein degradation agent is Proteinase K
and the heater or thermal source is used to inactivate the protein
degradation agent.
[0048] In some embodiments, the device also comprises a plurality
of alternating current (AC) electrodes within the housing, the AC
electrodes capable of being configured to be selectively energized
to establish dielectrophoretic (DEP) high field and
dielectrophoretic (DEP) low field regions, whereby AC
electrokinetic effects provide for concentration of cells in low
field regions of the device. In some embodiments, the electrodes
are selectively energized to provide the first AC electrokinetic
field region and subsequently or continuously selectively energized
to provide the second AC electrokinetic field region. For example,
further description of the electrodes and the concentration of
cells in DEP fields is found in PCT patent publication WO
2009/146143 A2, which is incorporated herein for such
disclosure.
[0049] In some embodiments, the device comprises a second reservoir
comprising an eluant. The eluant is any fluid suitable for eluting
the isolated nucleic acid from the device. In some instances the
eluant is water or a buffer. In some instances, the eluant
comprises reagents required for a DNA sequencing method.
[0050] Also provided herein are systems and devices comprising a
plurality of alternating current (AC) electrodes, the AC electrodes
configured to be selectively energized to establish
dielectrophoretic (DEP) high field and dielectrophoretic (DEP) low
field regions. In some instances, AC electrokinetic effects provide
for concentration of cells in low field regions and/or
concentration (or collection or isolation) of molecules (e.g.,
macromolecules, such as nucleic acid) in high field regions of the
DEP field.
[0051] Also provided herein are systems and devices comprising a
plurality of direct current (DC) electrodes. In some embodiments,
the plurality of DC electrodes comprises at least two rectangular
electrodes, spread throughout the array. In some embodiments, the
electrodes are located at the edges of the array. In some
embodiments, DC electrodes are interspersed between AC
electrodes.
[0052] In some embodiments, a system or device described herein
comprises a means for manipulating nucleic acid. In some
embodiments, a system or device described herein includes a means
of performing enzymatic reactions. In other embodiments, a system
or device described herein includes a means of performing
polymerase chain reaction, isothermal amplification, ligation
reactions, restriction analysis, nucleic acid cloning,
transcription or translation assays, or other enzymatic-based
molecular biology assay.
[0053] In some embodiments, a system or device described herein
comprises a nucleic acid sequencer. The sequencer is optionally any
suitable DNA sequencing device including but not limited to a
Sanger sequencer, pyro-sequencer, ion semiconductor sequencer,
polony sequencer, sequencing by ligation device, DNA nanoball
sequencing device, sequencing by ligation device, or single
molecule sequencing device.
[0054] In some embodiments, a system or device described herein is
capable of maintaining a constant temperature. In some embodiments,
a system or device described herein is capable of cooling the array
or chamber. In some embodiments, a system or device described
herein is capable of heating the array or chamber. In some
embodiments, a system or device described herein comprises a
thermocycler. In some embodiments, the devices disclosed herein
comprises a localized temperature control element. In some
embodiments, the devices disclosed herein are capable of both
sensing and controlling temperature.
[0055] In some embodiments, the devices further comprise heating or
thermal elements. In some embodiments, a heating or thermal element
is localized underneath an electrode. In some embodiments, the
heating or thermal elements comprise a metal. In some embodiments,
the heating or thermal elements comprise tantalum, aluminum,
tungsten, or a combination thereof. Generally, the temperature
achieved by a heating or thermal element is proportional to the
current running through it. In some embodiments, the devices
disclosed herein comprise localized cooling elements. In some
embodiments, heat resistant elements are placed directly under the
exposed electrode array. In some embodiments, the devices disclosed
herein are capable of achieving and maintaining a temperature
between about 20.degree. C. and about 120.degree. C. In some
embodiments, the devices disclosed herein are capable of achieving
and maintaining a temperature between about 30.degree. C. and about
100.degree. C. In other embodiments, the devices disclosed herein
are capable of achieving and maintaining a temperature between
about 20.degree. C. and about 95.degree. C. In some embodiments,
the devices disclosed herein are capable of achieving and
maintaining a temperature between about 25.degree. C. and about
90.degree. C., between about 25.degree. C. and about 85.degree. C.,
between about 25.degree. C. and about 75.degree. C., between about
25.degree. C. and about 65.degree. C. or between about 25.degree.
C. and about 55.degree. C. In some embodiments, the devices
disclosed herein are capable of achieving and maintaining a
temperature of about 20.degree. C., about 30.degree. C., about
40.degree. C., about 50.degree. C., about 60.degree. C., about
70.degree. C., about 80.degree. C., about 90.degree. C., about
100.degree. C., about 110.degree. C. or about 120.degree. C.
Electrodes
[0056] The plurality of alternating current electrodes are
optionally configured in any manner suitable for the separation
processes described herein. For example, further description of the
system or device including electrodes and/or concentration of cells
in DEP fields is found in PCT patent publication WO 2009/146143,
which is incorporated herein for such disclosure.
[0057] In some embodiments, the electrodes disclosed herein can
comprise any suitable metal. In some embodiments, the electrodes
can include but are not limited to: aluminum, copper, carbon, iron,
silver, gold, palladium, platinum, iridium, platinum iridium alloy,
ruthenium, rhodium, osmium, tantalum, titanium, tungsten,
polysilicon, and indium tin oxide, or combinations thereof, as well
as silicide materials such as platinum silicide, titanium silicide,
gold silicide, or tungsten silicide. In some embodiments, the
electrodes can comprise a conductive ink capable of being
screen-printed.
[0058] In some embodiments, the edge to edge (E2E) to diameter
ratio of an electrode is about 0.5 mm to about 5 mm. In some
embodiments, the E2E to diameter ratio is about 1 mm to about 4 mm.
In some embodiments, the E2E to diameter ratio is about 1 mm to
about 3 mm. In some embodiments, the E2E to diameter ratio is about
1 mm to about 2 mm. In some embodiments, the E2E to diameter ratio
is about 2 mm to about 5 mm. In some embodiments, the E2E to
diameter ratio is about 1 mm. In some embodiments, the E2E to
diameter ratio is about 2 mm. In some embodiments, the E2E to
diameter ratio is about 3 mm. In some embodiments, the E2E to
diameter ratio is about 4 mm. In some embodiments, the E2E to
diameter ratio is about 5 mm.
[0059] In some embodiments, the electrodes disclosed herein are
dry-etched. In some embodiments, the electrodes are wet etched. In
some embodiments, the electrodes undergo a combination of dry
etching and wet etching.
[0060] In some embodiments, each electrode is individually
site-controlled.
[0061] In some embodiments, an array of electrodes is controlled as
a unit.
[0062] In some embodiments, a passivation layer is employed. In
some embodiments, a passivation layer can be formed from any
suitable material known in the art. In some embodiments, the
passivation layer comprises silicon nitride. In some embodiments,
the passivation layer comprises silicon dioxide. In some
embodiments, the passivation layer has a relative electrical
permittivity of from about 2.0 to about 8.0. In some embodiments,
the passivation layer has a relative electrical permittivity of
from about 3.0 to about 8.0, about 4.0 to about 8.0 or about 5.0 to
about 8.0. In some embodiments, the passivation layer has a
relative electrical permittivity of about 2.0 to about 4.0. In some
embodiments, the passivation layer has a relative electrical
permittivity of from about 2.0 to about 3.0. In some embodiments,
the passivation layer has a relative electrical permittivity of
about 2.0, about 2.5, about 3.0, about 3.5 or about 4.0.
[0063] In some embodiments, the passivation layer is between about
0.1 microns and about 10 microns in thickness. In some embodiments,
the passivation layer is between about 0.5 microns and 8 microns in
thickness. In some embodiments, the passivation layer is between
about 1.0 micron and 5 microns in thickness. In some embodiments,
the passivation layer is between about 1.0 micron and 4 microns in
thickness. In some embodiments, the passivation layer is between
about 1.0 micron and 3 microns in thickness. In some embodiments,
the passivation layer is between about 0.25 microns and 2 microns
in thickness. In some embodiments, the passivation layer is between
about 0.25 microns and 1 micron in thickness.
[0064] In some embodiments, the passivation layer is comprised of
any suitable insulative low k dielectric material, including but
not limited to silicon nitride or silicon dioxide. In some
embodiments, the passivation layer is chosen from the group
consisting of polyamids, carbon, doped silicon nitride, carbon
doped silicon dioxide, fluorine doped silicon nitride, fluorine
doped silicon dioxide, porous silicon dioxide, or any combinations
thereof. In some embodiments, the passivation layer can comprise a
dielectric ink capable of being screen-printed.
Electrode Geometry
[0065] In some embodiments, the electrodes disclosed herein can be
arranged in any manner suitable for practicing the methods
disclosed herein.
[0066] In some embodiments, the electrodes are in a dot
configuration, e.g. the electrodes comprises a generally circular
or round configuration. In some embodiments, the angle of
orientation between dots is from about 25.degree. to about
60.degree.. In some embodiments, the angle of orientation between
dots is from about 30.degree. to about 55.degree.. In some
embodiments, the angle of orientation between dots is from about
30.degree. to about 50.degree.. In some embodiments, the angle of
orientation between dots is from about 35.degree. to about
45.degree.. In some embodiments, the angle of orientation between
dots is about 25.degree.. In some embodiments, the angle of
orientation between dots is about 30.degree.. In some embodiments,
the angle of orientation between dots is about 35.degree.. In some
embodiments, the angle of orientation between dots is about
40.degree.. In some embodiments, the angle of orientation between
dots is about 45.degree.. In some embodiments, the angle of
orientation between dots is about 50.degree.. In some embodiments,
the angle of orientation between dots is about 55.degree.. In some
embodiments, the angle of orientation between dots is about
60.degree..
[0067] In some embodiments, the electrodes are in a substantially
elongated configuration.
[0068] In some embodiments, the electrodes are in a configuration
resembling wavy or nonlinear lines. In some embodiments, the array
of electrodes is in a wavy or nonlinear line configuration, wherein
the configuration comprises a repeating unit comprising the shape
of a pair of dots connected by a linker, wherein the dots and
linker define the boundaries of the electrode, wherein the linker
tapers inward towards or at the midpoint between the pair of dots,
wherein the diameters of the dots are the widest points along the
length of the repeating unit, wherein the edge to edge distance
between a parallel set of repeating units is equidistant, or
roughly equidistant. In some embodiments, the electrodes are strips
resembling wavy lines, as depicted in FIG. 8. In some embodiments,
the edge to edge distance between the electrodes is equidistant, or
roughly equidistant throughout the wavy line configuration. In some
embodiments, the use of wavy line electrodes, as disclosed herein,
lead to an enhanced DEP field gradient.
[0069] In some embodiments, the electrodes disclosed herein are in
a planar configuration. In some embodiments, the electrodes
disclosed herein are in a non-planar configuration.
[0070] In some embodiments, the devices disclosed herein surface
selectively captures biomolecules on its surface. For example, the
devices disclosed herein may capture biomolecules, such as nucleic
acids, by, for example, a. nucleic acid hybridization; b.
antibody--antigen interactions; c. biotin--avidin interactions; d.
ionic or electrostatic interactions; or e. any combination thereof.
The devices disclosed herein, therefore, may incorporate a
functionalized surface which includes capture molecules, such as
complementary nucleic acid probes, antibodies or other protein
captures capable of capturing biomolecules (such as nucleic acids),
biotin or other anchoring captures capable of capturing
complementary target molecules such as avidin, capture molecules
capable of capturing biomolecules (such as nucleic acids) by ionic
or electrostatic interactions, or any combination thereof.
[0071] In some embodiments, the surface is functionalized to
minimize and/or inhibit nonspecific binding interactions by: a.
polymers (e.g., polyethylene glycol PEG); b. ionic or electrostatic
interactions; c. surfactants; or d. any combination thereof. In
some embodiments, the methods disclosed herein include use of
additives which reduce non-specific binding interactions by
interfering in such interactions, such as Tween 20 and the like,
bovine serum albumin, nonspecific immunoglobulins, etc.
[0072] In some embodiments, the device comprises a plurality of
microelectrode devices oriented (a) flat side by side, (b) facing
vertically, or (c) facing horizontally. In other embodiments, the
electrodes are in a sandwiched configuration, e.g. stacked on top
of each other in a vertical format.
Hydrogels
[0073] Overlaying electrode structures with one or more layers of
materials can reduce the deleterious electrochemistry effects,
including but not limited to electrolysis reactions, heating, and
chaotic fluid movement that may occur on or near the electrodes,
and still allow the effective separation of cells, bacteria, virus,
nanoparticles, DNA, and other biomolecules to be carried out. In
some embodiments, the materials layered over the electrode
structures may be one or more porous layers. In other embodiments,
the one or more porous layers is a polymer layer. In other
embodiments, the one or more porous layers is a hydrogel.
[0074] In general, the hydrogel should have sufficient mechanical
strength and be relatively chemically inert such that it will be
able to endure the electrochemical effects at the electrode surface
without disconfiguration or decomposition. In general, the hydrogel
is sufficiently permeable to small aqueous ions, but keeps
biomolecules away from the electrode surface.
[0075] In some embodiments, the hydrogel is a single layer, or
coating.
[0076] In some embodiments, the hydrogel comprises a gradient of
porosity, wherein the bottom of the hydrogel layer has greater
porosity than the top of the hydrogel layer.
[0077] In some embodiments, the hydrogel comprises multiple layers
or coatings. In some embodiments, the hydrogel comprises two coats.
In some embodiments, the hydrogel comprises three coats. In some
embodiments, the bottom (first) coating has greater porosity than
subsequent coatings. In some embodiments, the top coat is has less
porosity than the first coating. In some embodiments, the top coat
has a mean pore diameter that functions as a size cut-off for
particles of greater than 100 picometers in diameter.
[0078] In some embodiments, the hydrogel has a conductivity from
about 0.001 S/m to about 10 S/m. In some embodiments, the hydrogel
has a conductivity from about 0.01 S/m to about 10 S/m. In some
embodiments, the hydrogel has a conductivity from about 0.1 S/m to
about 10 S/m. In some embodiments, the hydrogel has a conductivity
from about 1.0 S/m to about 10 S/m. In some embodiments, the
hydrogel has a conductivity from about 0.01 S/m to about 5 S/m. In
some embodiments, the hydrogel has a conductivity from about 0.01
S/m to about 4 S/m. In some embodiments, the hydrogel has a
conductivity from about 0.01 S/m to about 3 S/m. In some
embodiments, the hydrogel has a conductivity from about 0.01 S/m to
about 2 S/m. In some embodiments, the hydrogel has a conductivity
from about 0.1 S/m to about 5 S/m. In some embodiments, the
hydrogel has a conductivity from about 0.1 S/m to about 4 S/m. In
some embodiments, the hydrogel has a conductivity from about 0.1
S/m to about 3 S/m. In some embodiments, the hydrogel has a
conductivity from about 0.1 S/m to about 2 S/m. In some
embodiments, the hydrogel has a conductivity from about 0.1 S/m to
about 1.5 S/m. In some embodiments, the hydrogel has a conductivity
from about 0.1 S/m to about 1.0 S/m.
[0079] In some embodiments, the hydrogel has a conductivity of
about 0.1 S/m. In some embodiments, the hydrogel has a conductivity
of about 0.2 S/m. In some embodiments, the hydrogel has a
conductivity of about 0.3 S/m. In some embodiments, the hydrogel
has a conductivity of about 0.4 S/m. In some embodiments, the
hydrogel has a conductivity of about 0.5 S/m. In some embodiments,
the hydrogel has a conductivity of about 0.6 S/m. In some
embodiments, the hydrogel has a conductivity of about 0.7 S/m. In
some embodiments, the hydrogel has a conductivity of about 0.8 S/m.
In some embodiments, the hydrogel has a conductivity of about 0.9
S/m. In some embodiments, the hydrogel has a conductivity of about
1.0 S/m.
[0080] In some embodiments, the hydrogel has a thickness from about
0.1 microns to about 10 microns. In some embodiments, the hydrogel
has a thickness from about 0.1 microns to about 5 microns. In some
embodiments, the hydrogel has a thickness from about 0.1 microns to
about 4 microns. In some embodiments, the hydrogel has a thickness
from about 0.1 microns to about 3 microns. In some embodiments, the
hydrogel has a thickness from about 0.1 microns to about 2 microns.
In some embodiments, the hydrogel has a thickness from about 1
micron to about 5 microns. In some embodiments, the hydrogel has a
thickness from about 1 micron to about 4 microns. In some
embodiments, the hydrogel has a thickness from about 1 micron to
about 3 microns. In some embodiments, the hydrogel has a thickness
from about 1 micron to about 2 microns. In some embodiments, the
hydrogel has a thickness from about 0.5 microns to about 1
micron.
[0081] In some embodiments, the viscosity of a hydrogel solution
prior to spin-coating ranges from about 0.5 cP to about 5 cP. In
some embodiments, a single coating of hydrogel solution has a
viscosity of between about 0.75 cP and 5 cP prior to spin-coating.
In some embodiments, in a multi-coat hydrogel, the first hydrogel
solution has a viscosity from about 0.5 cP to about 1.5 cP prior to
spin coating. In some embodiments, the second hydrogel solution has
a viscosity from about 1 cP to about 3 cP. The viscosity of the
hydrogel solution is based on the polymers concentration (0.1%-10%)
and polymers molecular weight (10,000 to 300,000) in the solvent
and the starting viscosity of the solvent.
[0082] In some embodiments, the first hydrogel coating has a
thickness between about 0.5 microns and 1 micron. In some
embodiments, the first hydrogel coating has a thickness between
about 0.5 microns and 0.75 microns. In some embodiments, the first
hydrogel coating has a thickness between about 0.75 and 1 micron.
In some embodiments, the second hydrogel coating has a thickness
between about 0.2 microns and 0.5 microns. In some embodiments, the
second hydrogel coating has a thickness between about 0.2 and 0.4
microns. In some embodiments, the second hydrogel coating has a
thickness between about 0.2 and 0.3 microns. In some embodiments,
the second hydrogel coating has a thickness between about 0.3 and
0.4 microns.
[0083] In some embodiments, the hydrogel comprises any suitable
synthetic polymer forming a hydrogel. In general, any sufficiently
hydrophilic and polymerizable molecule may be utilized in the
production of a synthetic polymer hydrogel for use as disclosed
herein. Polymerizable moieties in the monomers may include alkenyl
moieties including but not limited to substituted or unsubstituted
.alpha.,.beta., unsaturated carbonyls wherein the double bond is
directly attached to a carbon which is double bonded to an oxygen
and single bonded to another oxygen, nitrogen, sulfur, halogen, or
carbon; vinyl, wherein the double bond is singly bonded to an
oxygen, nitrogen, halogen, phosphorus or sulfur; allyl, wherein the
double bond is singly bonded to a carbon which is bonded to an
oxygen, nitrogen, halogen, phosphorus or sulfur; homoallyl, wherein
the double bond is singly bonded to a carbon which is singly bonded
to another carbon which is then singly bonded to an oxygen,
nitrogen, halogen, phosphorus or sulfur; alkynyl moieties wherein a
triple bond exists between two carbon atoms. In some embodiments,
acryloyl or acrylamido monomers such as acrylates, methacrylates,
acrylamides, methacrylamides, etc., are useful for formation of
hydrogels as disclosed herein. More preferred acrylamido monomers
include acrylamides, N-substituted acrylamides, N-substituted
methacrylamides, and methacrylamide. In some embodiments, a
hydrogel comprises polymers such as epoxide-based polymers,
vinyl-based polymers, allyl-based polymers, homoallyl-based
polymers, cyclic anhydride-based polymers, ester-based polymers,
ether-based polymers, alkylene-glycol based polymers (e.g.,
polypropylene glycol), and the like.
[0084] In some embodiments, the hydrogel comprises
polyhydroxyethylmethacrylate (pHEMA), cellulose acetate, cellulose
acetate phthalate, cellulose acetate butyrate, or any appropriate
acrylamide or vinyl-based polymer, or a derivative thereof.
[0085] In some embodiments, the hydrogel is applied by vapor
deposition.
[0086] In some embodiments, the hydrogel is polymerized via
atom-transfer radical-polymerization via (ATRP).
[0087] In some embodiments, the hydrogel is polymerized via
reversible addition--fragmentation chain-transfer (RAFT)
polymerization.
[0088] In some embodiments, additives are added to a hydrogel to
increase conductivity of the gel. In some embodiments, hydrogel
additives are conductive polymers (e.g., PEDOT: PSS), salts (e.g.,
copper chloride), metals (e.g., gold), plasticizers (e.g., PEG200,
PEG 400, or PEG 600), or co-solvents.
[0089] In some embodiments, the hydrogel also comprises compounds
or materials which help maintain the stability of the DNA hybrids,
including, but not limited to histidine, histidine peptides,
polyhistidine, lysine, lysine peptides, and other cationic
compounds or substances.
Dielectrophoretic Fields
[0090] In some embodiments, the methods, devices and systems
described herein provide a mechanism to collect, separate, or
isolate cells, particles, and/or molecules (such as nucleic acid)
from a fluid material (which optionally contains other materials,
such as contaminants, residual cellular material, or the like).
[0091] In some embodiments, an AC electrokinetic field is generated
to collect, separate or isolate biomolecules, such as nucleic
acids. In some embodiments, the AC electrokinetic field is a
dielectrophoretic field. Accordingly, in some embodiments
dielectrophoresis (DEP) is utilized in various steps of the methods
described herein.
[0092] In some embodiments, the devices and systems described
herein are capable of generating DEP fields, and the like. In
specific embodiments, DEP is used to concentrate cells and/or
nucleic acids (e.g., concurrently or at different times). In
certain embodiments, methods described herein further comprise
energizing the array of electrodes so as to produce the first,
second, and any further optional DEP fields. In some embodiments,
the devices and systems described herein are capable of being
energized so as to produce the first, second, and any further
optional DEP fields.
[0093] DEP is a phenomenon in which a force is exerted on a
dielectric particle when it is subjected to a non-uniform electric
field. Depending on the step of the methods described herein,
aspects of the devices and systems described herein, and the like,
the dielectric particle in various embodiments herein is a
biological cell and/or a molecule, such as a nucleic acid molecule.
Different steps of the methods described herein or aspects of the
devices or systems described herein may be utilized to isolate and
separate different components, such as intact cells or other
particular material; further, different field regions of the DEP
field may be used in different steps of the methods or aspects of
the devices and systems described herein. This dielectrophoretic
force does not require the particle to be charged. In some
instances, the strength of the force depends on the medium and the
specific particles' electrical properties, on the particles' shape
and size, as well as on the frequency of the electric field. In
some instances, fields of a particular frequency selectivity
manipulate particles. In certain aspects described herein, these
processes allow for the separation of cells and/or smaller
particles (such as molecules, including nucleic acid molecules)
from other components (e.g., in a fluid medium) or each other.
[0094] In various embodiments provided herein, a method described
herein comprises producing a first DEP field region and a second
DEP field region with the array. In various embodiments provided
herein, a device or system described herein is capable of producing
a first DEP field region and a second DEP field region with the
array. In some instances, the first and second field regions are
part of a single field (e.g., the first and second regions are
present at the same time, but are found at different locations
within the device and/or upon the array). In some embodiments, the
first and second field regions are different fields (e.g. the first
region is created by energizing the electrodes at a first time, and
the second region is created by energizing the electrodes a second
time). In specific aspects, the first DEP field region is suitable
for concentrating or isolating cells (e.g., into a low field DEP
region). In some embodiments, the second DEP field region is
suitable for concentrating smaller particles, such as molecules
(e.g., nucleic acid), for example into a high field DEP region. In
some instances, a method described herein optionally excludes use
of either the first or second DEP field region.
[0095] In some embodiments, the first DEP field region is in the
same chamber of a device as disclosed herein as the second DEP
field region. In some embodiments, the first DEP field region and
the second DEP field region occupy the same area of the array of
electrodes.
[0096] In some embodiments, the first DEP field region is in a
separate chamber of a device as disclosed herein, or a separate
device entirely, from the second DEP field region.
First DEP Field Region
[0097] In some aspects, e.g., high conductance buffers (>100
mS/m), the method described herein comprises applying a fluid
comprising cells or other particulate material to a device
comprising an array of electrodes, and, thereby, concentrating the
cells in a first DEP field region. In some aspects, the devices and
systems described herein are capable of applying a fluid comprising
cells or other particulate material to the device comprising an
array of electrodes, and, thereby, concentrating the cells in a
first DEP field region. Subsequent or concurrent second, or
optional third and fourth DEP regions, may collect or isolate other
fluid components, including biomolecules, such as nucleic
acids.
[0098] The first DEP field region may be any field region suitable
for concentrating cells from a fluid. For this application, the
cells are generally concentrated near the array of electrodes. In
some embodiments, the first DEP field region is a dielectrophoretic
low field region. In some embodiments, the first DEP field region
is a dielectrophoretic high field region. In some aspects, e.g. low
conductance buffers (<100 mS/m), the method described herein
comprises applying a fluid comprising cells to a device comprising
an array of electrodes, and, thereby, concentrating the cells or
other particulate material in a first DEP field region.
[0099] In some aspects, the devices and systems described herein
are capable of applying a fluid comprising cells or other
particulate material to the device comprising an array of
electrodes, and concentrating the cells in a first DEP field
region. In various embodiments, the first DEP field region may be
any field region suitable for concentrating cells from a fluid. In
some embodiments, the cells are concentrated on the array of
electrodes. In some embodiments, the cells are captured in a
dielectrophoretic high field region. In some embodiments, the cells
are captured in a dielectrophoretic low-field region. High versus
low field capture is generally dependent on the conductivity of the
fluid, wherein generally, the crossover point is between about
300-500 mS/m. In some embodiments, the first DEP field region is a
dielectrophoretic low field region performed in fluid conductivity
of greater than about 300 mS/m. In some embodiments, the first DEP
field region is a dielectrophoretic low field region performed in
fluid conductivity of less than about 300 mS/m. In some
embodiments, the first DEP field region is a dielectrophoretic high
field region performed in fluid conductivity of greater than about
300 mS/m. In some embodiments, the first DEP field region is a
dielectrophoretic high field region performed in fluid conductivity
of less than about 300 mS/m. In some embodiments, the first DEP
field region is a dielectrophoretic low field region performed in
fluid conductivity of greater than about 500 mS/m. In some
embodiments, the first DEP field region is a dielectrophoretic low
field region performed in fluid conductivity of less than about 500
mS/m. In some embodiments, the first DEP field region is a
dielectrophoretic high field region performed in fluid conductivity
of greater than about 500 mS/m. In some embodiments, the first DEP
field region is a dielectrophoretic high field region performed in
fluid conductivity of less than about 500 mS/m.
[0100] In some embodiments, the first dielectrophoretic field
region is produced by an alternating current. The alternating
current has any amperage, voltage, frequency, and the like suitable
for concentrating cells. In some embodiments, the first
dielectrophoretic field region is produced using an alternating
current having an amperage of 0.1 micro Amperes-10 Amperes; a
voltage of 1-50 Volts peak to peak; and/or a frequency of
1-10,000,000 Hz. In some embodiments, the first DEP field region is
produced using an alternating current having a voltage of 5-25
volts peak to peak. In some embodiments, the first DEP field region
is produced using an alternating current having a frequency of from
3-15 kHz. In some embodiments, the first DEP field region is
produced using an alternating current having an amperage of 1
milliamp to 1 amp. In some embodiments, the first DEP field region
is produced using an alternating current having an amperage of 0.1
micro Amperes-1 Ampere. In some embodiments, the first DEP field
region is produced using an alternating current having an amperage
of 1 micro Amperes-1 Ampere. In some embodiments, the first DEP
field region is produced using an alternating current having an
amperage of 100 micro Amperes-1 Ampere. In some embodiments, the
first DEP field region is produced using an alternating current
having an amperage of 500 micro Amperes-500 milli Amperes. In some
embodiments, the first DEP field region is produced using an
alternating current having a voltage of 1-25 Volts peak to peak. In
some embodiments, the first DEP field region is produced using an
alternating current having a voltage of 1-10 Volts peak to peak. In
some embodiments, the first DEP field region is produced using an
alternating current having a voltage of 25-50 Volts peak to peak.
In some embodiments, the first DEP field region is produced using a
frequency of from 10-1,000,000 Hz. In some embodiments, the first
DEP field region is produced using a frequency of from 100-100,000
Hz. In some embodiments, the first DEP field region is produced
using a frequency of from 100-10,000 Hz. In some embodiments, the
first DEP field region is produced using a frequency of from
10,000-100,000 Hz. In some embodiments, the first DEP field region
is produced using a frequency of from 100,000-1,000,000 Hz.
[0101] In some embodiments, the first dielectrophoretic field
region is produced by a direct current. The direct current has any
amperage, voltage, frequency, and the like suitable for
concentrating cells. In some embodiments, the first
dielectrophoretic field region is produced using a direct current
having an amperage of 0.1 micro Amperes-1 Amperes; a voltage of 10
milli Volts-10 Volts; and/or a pulse width of 1 milliseconds-1000
seconds and a pulse frequency of 0.001-1000 Hz. In some
embodiments, the first DEP field region is produced using a direct
current having an amperage of 1 micro Amperes-1 Amperes. In some
embodiments, the first DEP field region is produced using a direct
current having an amperage of 100 micro Amperes-500 milli Amperes.
In some embodiments, the first DEP field region is produced using a
direct current having an amperage of 1 milli Amperes-1 Amperes. In
some embodiments, the first DEP field region is produced using a
direct current having an amperage of 1 micro Amperes-1 milli
Amperes. In some embodiments, the first DEP field region is
produced using a direct current having a pulse width of 500
milliseconds-500 seconds. In some embodiments, the first DEP field
region is produced using a direct current having a pulse width of
500 milliseconds-100 seconds. In some embodiments, the first DEP
field region is produced using a direct current having a pulse
width of 1 second-1000 seconds. In some embodiments, the first DEP
field region is produced using a direct current having a pulse
width of 500 milliseconds-1 second. In some embodiments, the first
DEP field region is produced using a pulse frequency of 0.01-1000
Hz. In some embodiments, the first DEP field region is produced
using a pulse frequency of 0.1-100 Hz. In some embodiments, the
first DEP field region is produced using a pulse frequency of 1-100
Hz. In some embodiments, the first DEP field region is produced
using a pulse frequency of 100-1000 Hz.
[0102] In some embodiments, the fluid comprises a mixture of cell
types. For example, blood comprises red blood cells and white blood
cells. Environmental samples comprise many types of cells and other
particulate material over a wide range of concentrations. In some
embodiments, one cell type (or any number of cell types less than
the total number of cell types comprising the sample) is
preferentially concentrated in the first DEP field. Without
limitation, this embodiment is beneficial for focusing the nucleic
acid isolation procedure on a particular environmental contaminant,
such as a fecal coliform bacterium, whereby DNA sequencing may be
used to identify the source of the contaminant. In another
non-limiting example, the first DEP field is operated in a manner
that specifically concentrates viruses and not cells (e.g., in a
fluid with conductivity of greater than 300 mS/m, viruses
concentrate in a DEP high field region, while larger cells will
concentrate in a DEP low field region).
[0103] In some embodiments, a method, device or system described
herein is suitable for isolating or separating specific cell types.
In some embodiments, the DEP field of the method, device or system
is specifically tuned to allow for the separation or concentration
of a specific type of cell into a field region of the DEP field. In
some embodiments, a method, device or system described herein
provides more than one field region wherein more than one type of
cell is isolated or concentrated. In some embodiments, a method,
device, or system described herein is tunable so as to allow
isolation or concentration of different types of cells within the
DEP field regions thereof. In some embodiments, a method provided
herein further comprises tuning the DEP field. In some embodiments,
a device or system provided herein is capable of having the DEP
field tuned. In some instances, such tuning may be in providing a
DEP particularly suited for the desired purpose. For example,
modifications in the array, the energy, or another parameter are
optionally utilized to tune the DEP field. Tuning parameters for
finer resolution include electrode diameter, edge to edge distance
between electrodes, voltage, frequency, fluid conductivity and
hydrogel composition.
[0104] In some embodiments, the first DEP field region comprises
the entirety of an array of electrodes. In some embodiments, the
first DEP field region comprises a portion of an array of
electrodes. In some embodiments, the first DEP field region
comprises about 90%, about 80%, about 70%, about 60%, about 50%,
about 40%, about 30%, about 25%, about 20%, or about 10% of an
array of electrodes. In some embodiments, the first DEP field
region comprises about a third of an array of electrodes.
Second DEP Field Region
[0105] In one aspect, following lysis of the cells (as provided
below), the methods described herein involve concentrating the
nucleic acid in a second DEP field region. In another aspect, the
devices and systems described herein are capable of concentrating
the nucleic acid in a second DEP field region. In some embodiments,
the second DEP field region is any field region suitable for
concentrating nucleic acids. In some embodiments, the nucleic acids
are concentrated on the array of electrodes. In some embodiments,
the second DEP field region is a dielectrophoretic high field
region. The second DEP field region is, optionally, the same as the
first DEP field region.
[0106] In some embodiments, the second dielectrophoretic field
region is produced by an alternating current. In some embodiments,
the alternating current has any amperage, voltage, frequency, and
the like suitable for concentrating nucleic acids. In some
embodiments, the second dielectrophoretic field region is produced
using an alternating current having an amperage of 0.1 micro
Amperes-10 Amperes; a voltage of 1-50 Volts peak to peak; and/or a
frequency of 1-10,000,000 Hz. In some embodiments, the second DEP
field region is produced using an alternating current having an
amperage of 0.1 micro Amperes-1 Ampere. In some embodiments, the
second DEP field region is produced using an alternating current
having an amperage of 1 micro Amperes-1 Ampere. In some
embodiments, the second DEP field region is produced using an
alternating current having an amperage of 100 micro Amperes-1
Ampere. In some embodiments, the second DEP field region is
produced using an alternating current having an amperage of 500
micro Amperes-500 milli Amperes. In some embodiments, the second
DEP field region is produced using an alternating current having a
voltage of 1-25 Volts peak to peak. In some embodiments, the second
DEP field region is produced using an alternating current having a
voltage of 1-10 Volts peak to peak. In some embodiments, the second
DEP field region is produced using an alternating current having a
voltage of 25-50 Volts peak to peak. In some embodiments, the
second DEP field region is produced using a frequency of from
10-1,000,000 Hz. In some embodiments, the second DEP field region
is produced using a frequency of from 100-100,000 Hz. In some
embodiments, the second DEP field region is produced using a
frequency of from 100-10,000 Hz. In some embodiments, the second
DEP field region is produced using a frequency of from
10,000-100,000 Hz. In some embodiments, the second DEP field region
is produced using a frequency of from 100,000-1,000,000 Hz.
[0107] In some embodiments, the second dielectrophoretic field
region is produced by a direct current. In some embodiments, the
direct current has any amperage, voltage, frequency, and the like
suitable for concentrating nucleic acids. In some embodiments, the
second dielectrophoretic field region is produced using a direct
current having an amperage of 0.1 micro Amperes-1 Amperes; a
voltage of 10 milli Volts-10 Volts; and/or a pulse width of 1
milliseconds-1000 seconds and a pulse frequency of 0.001-1000 Hz.
In some embodiments, the second DEP field region is produced using
an alternating current having a voltage of 5-25 volts peak to peak.
In some embodiments, the second DEP field region is produced using
an alternating current having a frequency of from 3-15 kHz. In some
embodiments, the second DEP field region is produced using an
alternating current having an amperage of 1 milliamp to 1 amp. In
some embodiments, the second DEP field region is produced using a
direct current having an amperage of 1 micro Amperes-1 Amperes. In
some embodiments, the second DEP field region is produced using a
direct current having an amperage of 100 micro Amperes-500 milli
Amperes. In some embodiments, the second DEP field region is
produced using a direct current having an amperage of 1 milli
Amperes-1 Amperes. In some embodiments, the second DEP field region
is produced using a direct current having an amperage of 1 micro
Amperes-1 milli Amperes. In some embodiments, the second DEP field
region is produced using a direct current having a pulse width of
500 milliseconds-500 seconds. In some embodiments, the second DEP
field region is produced using a direct current having a pulse
width of 500 milliseconds-100 seconds. In some embodiments, the
second DEP field region is produced using a direct current having a
pulse width of 1 second-1000 seconds. In some embodiments, the
second DEP field region is produced using a direct current having a
pulse width of 500 milliseconds-1 second. In some embodiments, the
second DEP field region is produced using a pulse frequency of
0.01-1000 Hz. In some embodiments, the second DEP field region is
produced using a pulse frequency of 0.1-100 Hz. In some
embodiments, the second DEP field region is produced using a pulse
frequency of 1-100 Hz. In some embodiments, the second DEP field
region is produced using a pulse frequency of 100-1000 Hz.
[0108] In some embodiments, the second DEP field region comprises
the entirety of an array of electrodes. In some embodiments, the
second DEP field region comprises a portion of an array of
electrodes. In some embodiments, the second DEP field region
comprises about 90%, about 80%, about 70%, about 60%, about 50%,
about 40%, about 30%, about 25%, about 20%, or about 10% of an
array of electrodes. In some embodiments, the second DEP field
region comprises about a third of an array of electrodes.
Isolating Nucleic Acids
[0109] In one aspect, described herein is a method for isolating a
nucleic acid from a fluid comprising cells. In some embodiments,
the nucleic acids are initially inside the cells. As seen in FIG.
5, the method comprises concentrating the cells near a high field
region in some instances. In some embodiments, disclosed herein is
method for isolating a nucleic acid from a fluid comprising cells,
the method comprising: a. applying the fluid to a device, the
device comprising an array of electrodes; b. concentrating a
plurality of cells in a first AC electrokinetic (e.g.,
dielectrophoretic) field region; c. isolating nucleic acid in a
second AC electrokinetic (e.g., dielectrophoretic) field region;
and d. flushing cells away. In some instances, the cells are lysed
in the high field region. Following lysis, the nucleic acids remain
in the high field region and/or are concentrated in the high field
region. In some instances, residual cellular material is
concentrated near the low field region. In some embodiments, the
residual material is washed from the device and/or washed from the
nucleic acids. In some embodiments, the nucleic acid is
concentrated in the second AC electrokinetic field region.
[0110] In one aspect, described herein is a method for isolating a
nucleic acid from a fluid comprising cells or other particulate
material. In some embodiments, the nucleic acids are not inside the
cells (e.g., cell-free DNA in fluid). In some embodiments,
disclosed herein is a method for isolating a nucleic acid from a
fluid comprising cells or other particulate material, the method
comprising: a. applying the fluid to a device, the device
comprising an array of electrodes; b. concentrating a plurality of
cells in a first AC electrokinetic (e.g., dielectrophoretic) field
region; c. isolating nucleic acid in a second AC electrokinetic
(e.g., dielectrophoretic) field region; and d. flushing cells away.
In some embodiments, the method further comprises degrading
residual proteins after flushing cells away. FIG. 6 shows an
exemplary method for isolating extra-cellular nucleic acids from a
fluid comprising cells. In some embodiments, cells are concentrated
on or near a low field region and nucleic acids are concentrated on
or near a high field region. In some instances, the cells are
washed from the device and/or washed from the nucleic acids.
[0111] In one aspect, the methods, systems and devices described
herein isolate nucleic acid from a fluid comprising cells or other
particulate material. In one aspect, dielectrophoresis is used to
concentrate cells. In some embodiments, the fluid is a liquid,
optionally water or an aqueous solution or dispersion. In some
embodiments, the fluid is any suitable fluid including a bodily
fluid. Exemplary bodily fluids include blood, serum, plasma, bile,
milk, cerebrospinal fluid, gastric juice, ejaculate, mucus,
peritoneal fluid, saliva, sweat, tears, urine, and the like. In
some embodiments, nucleic acids are isolated from bodily fluids
using the methods, systems or devices described herein as part of a
medical therapeutic or diagnostic procedure, device or system. In
some embodiments, the fluid is tissues and/or cells solubilized
and/or dispersed in a fluid. For example, the tissue can be a
cancerous tumor from which nucleic acid can be isolated using the
methods, devices or systems described herein.
[0112] In some embodiments, the fluid is an environmental sample.
In some embodiments, the environmental sample is assayed or
monitored for the presence of a particular nucleic acid sequence
indicative of a certain contamination, infestation incidence or the
like. The environmental sample can also be used to determine the
source of a certain contamination, infestation incidence or the
like using the methods, devices or systems described herein.
Exemplary environmental samples include municipal wastewater,
industrial wastewater, water or fluid used in or produced as a
result of various manufacturing processes, lakes, rivers, oceans,
aquifers, ground water, storm water, plants or portions of plants,
animals or portions of animals, insects, municipal water supplies,
and the like.
[0113] In some embodiments, the fluid is a food or beverage. The
food or beverage can be assayed or monitored for the presence of a
particular nucleic acid sequence indicative of a certain
contamination, infestation incidence or the like. The food or
beverage can also be used to determine the source of a certain
contamination, infestation incidence or the like using the methods,
devices or systems described herein. In various embodiments, the
methods, devices and systems described herein can be used with one
or more of bodily fluids, environmental samples, and foods and
beverages to monitor public health or respond to adverse public
health incidences.
[0114] In some embodiments, the fluid is a growth medium. The
growth medium can be any medium suitable for culturing cells, for
example lysogeny broth (LB) for culturing E. coli, Ham's tissue
culture medium for culturing mammalian cells, and the like. The
medium can be a rich medium, minimal medium, selective medium, and
the like. In some embodiments, the medium comprises or consists
essentially of a plurality of clonal cells. In some embodiments,
the medium comprises a mixture of at least two species.
[0115] In some embodiments, the fluid is water.
[0116] The cells are any cell suitable for isolating nucleic acids
from as described herein. In various embodiments, the cells are
eukaryotic or prokaryotic. In various embodiments, the cells
consist essentially of a plurality of clonal cells or may comprise
at least two species and/or at least two strains.
[0117] In various embodiments, the cells are pathogen cells,
bacteria cells, plant cells, animal cells, insect cells, algae
cells, cyanobacterial cells, organelles and/or combinations
thereof. As used herein, "cells" include viruses and other intact
pathogenic microorganisms. The cells can be microorganisms or cells
from multi-cellular organisms. In some instances, the cells
originate from a solubilized tissue sample.
[0118] In various embodiments, the cells are wild-type or
genetically engineered. In some instances, the cells comprise a
library of mutant cells. In some embodiments, the cells are
randomly mutagenized such as having undergone chemical mutagenesis,
radiation mutagenesis (e.g. UV radiation), or a combination
thereof. In some embodiments, the cells have been transformed with
a library of mutant nucleic acid molecules.
[0119] In some embodiments, the fluid may also comprise other
particulate material. Such particulate material may be, for
example, inclusion bodies (e.g., ceroids or Mallory bodies),
cellular casts (e.g., granular casts, hyaline casts, cellular
casts, waxy casts and pseudo casts), Pick's bodies, Lewy bodies,
fibrillary tangles, fibril formations, cellular debris and other
particulate material. In some embodiments, particulate material is
an aggregated protein (e.g., beta-amyloid).
[0120] The fluid can have any conductivity including a high or low
conductivity. In some embodiments, the conductivity is between
about 1 .mu.S/m to about 10 mS/m. In some embodiments, the
conductivity is between about 10 .mu.S/m to about 10 mS/m. In other
embodiments, the conductivity is between about 50 .mu.S/m to about
10 mS/m. In yet other embodiments, the conductivity is between
about 100 .mu.S/m to about 10 mS/m, between about 100 .mu.S/m to
about 8 mS/m, between about 100 .mu.S/m to about 6 mS/m, between
about 100 .mu.S/m to about 5 mS/m, between about 100 .mu.S/m to
about 4 mS/m, between about 100 .mu.S/m to about 3 mS/m, between
about 100 .mu.S/m to about 2 mS/m, or between about 100 .mu.S/m to
about 1 mS/m.
[0121] In some embodiments, the conductivity is about 1 .mu.S/m. In
some embodiments, the conductivity is about 10 .mu.S/m. In some
embodiments, the conductivity is about 100 .mu.S/m. In some
embodiments, the conductivity is about 1 mS/m. In other
embodiments, the conductivity is about 2 mS/m. In some embodiments,
the conductivity is about 3 mS/m. In yet other embodiments, the
conductivity is about 4 mS/m. In some embodiments, the conductivity
is about 5 mS/m. In some embodiments, the conductivity is about 10
mS/m. In still other embodiments, the conductivity is about 100
mS/m. In some embodiments, the conductivity is about 1 S/m. In
other embodiments, the conductivity is about 10 S/m.
[0122] In some embodiments, the conductivity is at least 1 .mu.S/m.
In yet other embodiments, the conductivity is at least 10 .mu.S/m.
In some embodiments, the conductivity is at least 100 .mu.S/m. In
some embodiments, the conductivity is at least 1 mS/m. In
additional embodiments, the conductivity is at least 10 mS/m. In
yet other embodiments, the conductivity is at least 100 mS/m. In
some embodiments, the conductivity is at least 1 S/m. In some
embodiments, the conductivity is at least 10 S/m. In some
embodiments, the conductivity is at most 1 .mu.S/m. In some
embodiments, the conductivity is at most 10 .mu.S/m. In other
embodiments, the conductivity is at most 100 .mu.S/m. In some
embodiments, the conductivity is at most 1 mS/m. In some
embodiments, the conductivity is at most 10 mS/m. In some
embodiments, the conductivity is at most 100 mS/m. In yet other
embodiments, the conductivity is at most 1 S/m. In some
embodiments, the conductivity is at most 10 S/m.
[0123] In some embodiments, the fluid is a small volume of liquid
including less than 10 ml. In some embodiments, the fluid is less
than 8 ml. In some embodiments, the fluid is less than 5 ml. In
some embodiments, the fluid is less than 2 ml. In some embodiments,
the fluid is less than 1 ml. In some embodiments, the fluid is less
than 500 .mu.l. In some embodiments, the fluid is less than 200
.mu.l. In some embodiments, the fluid is less than 100 .mu.l. In
some embodiments, the fluid is less than 50 .mu.l. In some
embodiments, the fluid is less than 10 .mu.l. In some embodiments,
the fluid is less than 5 .mu.l. In some embodiments, the fluid is
less than 1 .mu.l.
[0124] In some embodiments, the quantity of fluid applied to the
device or used in the method comprises less than about 100,000,000
cells. In some embodiments, the fluid comprises less than about
10,000,000 cells. In some embodiments, the fluid comprises less
than about 1,000,000 cells. In some embodiments, the fluid
comprises less than about 100,000 cells. In some embodiments, the
fluid comprises less than about 10,000 cells. In some embodiments,
the fluid comprises less than about 1,000 cells.
[0125] In some embodiments, isolation of nucleic acid from a fluid
comprising cells or other particulate material with the devices,
systems and methods described herein takes less than about 30
minutes, less than about 20 minutes, less than about 15 minutes,
less than about 10 minutes, less than about 5 minutes or less than
about 1 minute. In other embodiments, isolation of nucleic acid
from a fluid comprising cells or other particulate material with
the devices, systems and methods described herein takes not more
than 30 minutes, not more than about 20 minutes, not more than
about 15 minutes, not more than about 10 minutes, not more than
about 5 minutes, not more than about 2 minutes or not more than
about 1 minute. In additional embodiments, isolation of nucleic
acid from a fluid comprising cells or other particulate material
with the devices, systems and methods described herein takes less
than about 15 minutes, preferably less than about 10 minutes or
less than about 5 minutes.
[0126] In some instances, extra-cellular DNA or other nucleic acid
(outside cells) is isolated from a fluid comprising cells of other
particulate material. In some embodiments, the fluid comprises
cells. In some embodiments, the fluid does not comprise cells.
Cell Lysis
[0127] In one aspect, following concentrating the cells in a first
dielectrophoretic field region, the method involves freeing nucleic
acids from the cells. In another aspect, the devices and systems
described herein are capable of freeing nucleic acids from the
cells. In some embodiments, the nucleic acids are freed from the
cells in the first DEP field region.
[0128] In some embodiments, the methods described herein free
nucleic acids from a plurality of cells by lysing the cells. In
some embodiments, the devices and systems described herein are
capable of freeing nucleic acids from a plurality of cells by
lysing the cells. One method of cell lysis involves applying a
direct current to the cells after isolation of the cells on the
array. The direct current has any suitable amperage, voltage, and
the like suitable for lysing cells. In some embodiments, the
current has a voltage of about 1 Volt to about 500 Volts. In some
embodiments, the current has a voltage of about 10 Volts to about
500 Volts. In other embodiments, the current has a voltage of about
10 Volts to about 250 Volts. In still other embodiments, the
current has a voltage of about 50 Volts to about 150 Volts. Voltage
is generally the driver of cell lysis, as high electric fields
result in failed membrane integrity.
[0129] In some embodiments, the direct current used for lysis
comprises one or more pulses having any duration, frequency, and
the like suitable for lysing cells. In some embodiments, a voltage
of about 100 volts is applied for about 1 millisecond to lyse
cells. In some embodiments, the voltage of about 100 volts is
applied 2 or 3 times over the source of a second.
[0130] In some embodiments, the frequency of the direct current
depends on volts/cm, pulse width, and the fluid conductivity. In
some embodiments, the pulse has a frequency of about 0.001 to about
1000 Hz. In some embodiments, the pulse has a frequency from about
10 to about 200 Hz. In other embodiments, the pulse has a frequency
of about 0.01 Hz-1000 Hz. In still other embodiments, the pulse has
a frequency of about 0.1 Hz-1000 Hz, about 1 Hz-1000 Hz, about 1
Hz-500 Hz, about 1 Hz-400 Hz, about 1 Hz-300 Hz, or about 1
Hz-about 250 Hz. In some embodiments, the pulse has a frequency of
about 0.1 Hz. In other embodiments, the pulse has a frequency of
about 1 Hz. In still other embodiments, the pulse has a frequency
of about 5 Hz, about 10 Hz, about 50 Hz, about 100 Hz, about 200
Hz, about 300 Hz, about 400 Hz, about 500 Hz, about 600 Hz, about
700 Hz, about 800 Hz, about 900 Hz or about 1000 Hz.
[0131] In other embodiments, the pulse has a duration of about 1
millisecond (ms)-1000 seconds (s). In some embodiments, the pulse
has a duration of about 10 ms-1000 s. In still other embodiments,
the pulse has a duration of about 100 ms-1000 s, about 1 s-1000 s,
about 1 s-500 s, about 1 s-250 s or about 1 s-150 s. In some
embodiments, the pulse has a duration of about 1 ms, about 10 ms,
about 100 ms, about 1 s, about 2 s, about 3 s, about 4 s, about 5
s, about 6 s, about 7 s, about 8 s, about 9 s, about 10 s, about 20
s, about 50 s, about 100 s, about 200 s, about 300 s, about 500 s
or about 1000 s. In some embodiments, the pulse has a frequency of
0.2 to 200 Hz with duty cycles from 10-50%.
[0132] In some embodiments, the direct current is applied once, or
as multiple pulses. Any suitable number of pulses may be applied
including about 1-20 pulses. There is any suitable amount of time
between pulses including about 1 millisecond-1000 seconds. In some
embodiments, the pulse duration is 0.01 to 10 seconds.
[0133] In some embodiments, the cells are lysed using other methods
in combination with a direct current applied to the isolated cells.
In yet other embodiments, the cells are lysed without use of direct
current. In various aspects, the devices and systems are capable of
lysing cells with direct current in combination with other means,
or may be capable of lysing cells without the use of direct
current. Any method of cell lysis known to those skilled in the art
may be suitable including, but not limited to application of a
chemical lysing agent (e.g., an acid), an enzymatic lysing agent,
heat, pressure, shear force, sonic energy, osmotic shock, or
combinations thereof. Lysozyme is an example of an enzymatic-lysing
agent.
Removal of Residual Material
[0134] In some embodiments, following concentration of the nucleic
acids in the second DEP field region, the method includes
optionally flushing residual material from the nucleic acid. In
some embodiments, the devices or systems described herein are
capable of optionally and/or comprising a reservoir comprising a
fluid suitable for flushing residual material from the nucleic
acid. In some embodiments, the nucleic acid is held near the array
of electrodes, such as in the second DEP field region, by
continuing to energize the electrodes. "Residual material" is
anything originally present in the fluid, originally present in the
cells, added during the procedure, created through any step of the
process including but not limited to lysis of the cells (i.e.
residual cellular material), and the like. For example, residual
material includes non-lysed cells, cell wall fragments, proteins,
lipids, carbohydrates, minerals, salts, buffers, plasma, and
undesired nucleic acids. In some embodiments, the lysed cellular
material comprises residual protein freed from the plurality of
cells upon lysis. It is possible that not all of the nucleic acid
will be concentrated in the second DEP field. In some embodiments,
a certain amount of nucleic acid is flushed with the residual
material.
[0135] In some embodiments, the residual material is flushed in any
suitable fluid, for example in water, TBE buffer, or the like. In
some embodiments, the residual material is flushed with any
suitable volume of fluid, flushed for any suitable period of time,
flushed with more than one fluid, or any other variation. In some
embodiments, the method of flushing residual material is related to
the desired level of isolation of the nucleic acid, with higher
purity nucleic acid requiring more stringent flushing and/or
washing. In other embodiments, the method of flushing residual
material is related to the particular starting material and its
composition. In some instances, a starting material that is high in
lipid requires a flushing procedure that involves a hydrophobic
fluid suitable for solubilizing lipids.
[0136] In some embodiments, the method includes degrading residual
material including residual protein. In some embodiments, the
devices or systems are capable of degrading residual material
including residual protein. For example, proteins are degraded by
one or more of chemical degradation (e.g. acid hydrolysis) and
enzymatic degradation. In some embodiments, the enzymatic
degradation agent is a protease. In other embodiments, the protein
degradation agent is Proteinase K. The optional step of degradation
of residual material is performed for any suitable time,
temperature, and the like. In some embodiments, the degraded
residual material (including degraded proteins) is flushed from the
nucleic acid.
[0137] In some embodiments, the agent used to degrade the residual
material is inactivated or degraded. In some embodiments, the
devices or systems are capable of degrading or inactivating the
agent used to degrade the residual material. In some embodiments,
an enzyme used to degrade the residual material is inactivated by
heat (e.g., 50 to 95.degree. C. for 5-15 minutes). For example,
enzymes including proteases, (for example, Proteinase K) are
degraded and/or inactivated using heat (typically, 15 minutes,
70.degree. C.). In some embodiments wherein the residual proteins
are degraded by an enzyme, the method further comprises
inactivating the degrading enzyme (e.g., Proteinase K) following
degradation of the proteins. In some embodiments, heat is provided
by a heating module in the device (temperature range, e.g., from 30
to 95.degree. C.).
[0138] The order and/or combination of certain steps of the method
can be varied. In some embodiments, the devices or methods are
capable of performing certain steps in any order or combination.
For example, in some embodiments, the residual material and the
degraded proteins are flushed in separate or concurrent steps. That
is, the residual material is flushed, followed by degradation of
residual proteins, followed by flushing degraded proteins from the
nucleic acid. In some embodiments, one first degrades the residual
proteins, and then flush both the residual material and degraded
proteins from the nucleic acid in a combined step.
[0139] In some embodiments, the nucleic acid are retained in the
device and optionally used in further procedures such as PCR or
other procedures manipulating or amplifying nucleic acid. In some
embodiments, the devices and systems are capable of performing PCR
or other optional procedures. In other embodiments, the nucleic
acids are collected and/or eluted from the device. In some
embodiments, the devices and systems are capable of allowing
collection and/or elution of nucleic acid from the device or
system. In some embodiments, the isolated nucleic acid is collected
by (i) turning off the second dielectrophoretic field region; and
(ii) eluting the nucleic acid from the array in an eluant.
Exemplary eluants include water, TE, TBE and L-Histidine
buffer.
Nucleic Acids and Yields Thereof
[0140] In some embodiments, the method, device, or system described
herein is optionally utilized to obtain, isolate, or separate any
desired nucleic acid that may be obtained from such a method,
device or system. Nucleic acids isolated by the methods, devices
and systems described herein include DNA (deoxyribonucleic acid),
RNA (ribonucleic acid), and combinations thereof. In some
embodiments, the nucleic acid is isolated in a form suitable for
sequencing or further manipulation of the nucleic acid, including
amplification, ligation or cloning.
[0141] In various embodiments, an isolated or separated nucleic
acid is a composition comprising nucleic acid that is free from at
least 99% by mass of other materials, free from at least 99% by
mass of residual cellular material (e.g., from lysed cells from
which the nucleic acid is obtained), free from at least 98% by mass
of other materials, free from at least 98% by mass of residual
cellular material, free from at least 95% by mass of other
materials, free from at least 95% by mass of residual cellular
material, free from at least 90% by mass of other materials, free
from at least 90% by mass of residual cellular material, free from
at least 80% by mass of other materials, free from at least 80% by
mass of residual cellular material, free from at least 70% by mass
of other materials, free from at least 70% by mass of residual
cellular material, free from at least 60% by mass of other
materials, free from at least 60% by mass of residual cellular
material, free from at least 50% by mass of other materials, free
from at least 50% by mass of residual cellular material, free from
at least 30% by mass of other materials, free from at least 30% by
mass of residual cellular material, free from at least 10% by mass
of other materials, free from at least 10% by mass of residual
cellular material, free from at least 5% by mass of other
materials, or free from at least 5% by mass of residual cellular
material.
[0142] In various embodiments, the nucleic acid has any suitable
purity. For example, if a DNA sequencing procedure can work with
nucleic acid samples having about 20% residual cellular material,
then isolation of the nucleic acid to 80% is suitable. In some
embodiments, the isolated nucleic acid comprises less than about
80%, less than about 70%, less than about 60%, less than about 50%,
less than about 40%, less than about 30%, less than about 20%, less
than about 10%, less than about 5%, or less than about 2%
non-nucleic acid cellular material and/or protein by mass. In some
embodiments, the isolated nucleic acid comprises greater than about
99%, greater than about 98%, greater than about 95%, greater than
about 90%, greater than about 80%, greater than about 70%, greater
than about 60%, greater than about 50%, greater than about 40%,
greater than about 30%, greater than about 20%, or greater than
about 10% nucleic acid by mass.
[0143] The nucleic acids are isolated in any suitable form
including unmodified, derivatized, fragmented, non-fragmented, and
the like. In some embodiments, the nucleic acid is collected in a
form suitable for sequencing. In some embodiments, the nucleic acid
is collected in a fragmented form suitable for shotgun-sequencing,
amplification or other manipulation. The nucleic acid may be
collected from the device in a solution comprising reagents used
in, for example, a DNA sequencing procedure, such as nucleotides as
used in sequencing by synthesis methods.
[0144] In some embodiments, the methods described herein result in
an isolated nucleic acid sample that is approximately
representative of the nucleic acid of the starting sample. In some
embodiments, the devices and systems described herein are capable
of isolating nucleic acid from a sample that is approximately
representative of the nucleic acid of the starting sample. That is,
the population of nucleic acids collected by the method, or capable
of being collected by the device or system, are substantially in
proportion to the population of nucleic acids present in the cells
in the fluid. In some embodiments, this aspect is advantageous in
applications in which the fluid is a complex mixture of many cell
types and the practitioner desires a nucleic acid-based procedure
for determining the relative populations of the various cell
types.
[0145] In some embodiments, the nucleic acid isolated using the
methods described herein or capable of being isolated by the
devices described herein is high-quality and/or suitable for using
directly in downstream procedures such as DNA sequencing, nucleic
acid amplification, such as PCR, or other nucleic acid
manipulation, such as ligation, cloning or further translation or
transformation assays. In some embodiments, the collected nucleic
acid comprises at most 0.01% protein. In some embodiments, the
collected nucleic acid comprises at most 0.5% protein. In some
embodiments, the collected nucleic acid comprises at most 0.1%
protein. In some embodiments, the collected nucleic acid comprises
at most 1% protein. In some embodiments, the collected nucleic acid
comprises at most 2% protein. In some embodiments, the collected
nucleic acid comprises at most 3% protein. In some embodiments, the
collected nucleic acid comprises at most 4% protein. In some
embodiments, the collected nucleic acid comprises at most 5%
protein.
[0146] In some embodiments, the nucleic acid isolated by the
methods described herein or capable of being isolated by the
devices described herein has a concentration of at least 0.5 ng/mL.
In some embodiments, the nucleic acid isolated by the methods
described herein or capable of being isolated by the devices
described herein has a concentration of at least 1 ng/mL. In some
embodiments, the nucleic acid isolated by the methods described
herein or capable of being isolated by the devices described herein
has a concentration of at least 5 ng/mL. In some embodiments, the
nucleic acid isolated by the methods described herein or capable of
being isolated by the devices described herein has a concentration
of at least 10 ng/ml.
[0147] In some embodiments, about 50 pico-grams of nucleic acid is
isolated from about 5,000 cells using the methods, systems or
devices described herein. In some embodiments, the methods, systems
or devices described herein yield at least 10 pico-grams of nucleic
acid from about 5,000 cells. In some embodiments, the methods,
systems or devices described herein yield at least 20 pico-grams of
nucleic acid from about 5,000 cells. In some embodiments, the
methods, systems or devices described herein yield at least 50
pico-grams of nucleic acid from about 5,000 cells. In some
embodiments, the methods, systems or devices described herein yield
at least 75 pico-grams of nucleic acid from about 5,000 cells. In
some embodiments, the methods, systems or devices described herein
yield at least 100 pico-grams of nucleic acid from about 5,000
cells. In some embodiments, the methods, systems or devices
described herein yield at least 200 pico-grams of nucleic acid from
about 5,000 cells. In some embodiments, the methods, systems or
devices described herein yield at least 300 pico-grams of nucleic
acid from about 5,000 cells. In some embodiments, the methods,
systems or devices described herein yield at least 400 pico-grams
of nucleic acid from about 5,000 cells. In some embodiments, the
methods, systems or devices described herein yield at least 500
pico-grams of nucleic acid from about 5,000 cells. In some
embodiments, the methods, systems or devices described herein yield
at least 1,000 pico-grams of nucleic acid from about 5,000 cells.
In some embodiments, the methods, systems or devices described
herein yield at least 10,000 pico-grams of nucleic acid from about
5,000 cells.
Assays and Applications
[0148] In some embodiments, the methods described herein further
comprise optionally amplifying the isolated nucleic acid by
polymerase chain reaction (PCR). In some embodiments, the PCR
reaction is performed on or near the array of electrodes or in the
device. In some embodiments, the device or system comprise a heater
and/or temperature control mechanisms suitable for
thermocycling.
[0149] PCR is optionally done using traditional thermocycling by
placing the reaction chemistry analytes in between two efficient
thermoconductive elements (e.g., aluminum or silver) and regulating
the reaction temperatures using TECs. Additional designs optionally
use infrared heating through optically transparent material like
glass or thermo polymers. In some instances, designs use smart
polymers or smart glass that comprise conductive wiring networked
through the substrate. This conductive wiring enables rapid thermal
conductivity of the materials and (by applying appropriate DC
voltage) provides the required temperature changes and gradients to
sustain efficient PCR reactions. In certain instances, heating is
applied using resistive chip heaters and other resistive elements
that will change temperature rapidly and proportionally to the
amount of current passing through them.
[0150] In some embodiments, used in conjunction with traditional
fluorometry (ccd, pmt, other optical detector, and optical
filters), fold amplification is monitored in real-time or on a
timed interval. In certain instances, quantification of final fold
amplification is reported via optical detection converted to AFU
(arbitrary fluorescence units correlated to analyze doubling) or
translated to electrical signal via impedance measurement or other
electrochemical sensing.
[0151] Given the small size of the micro electrode array, these
elements are optionally added around the micro electrode array and
the PCR reaction will be performed in the main sample processing
chamber (over the DEP array) or the analytes to be amplified are
optionally transported via fluidics to another chamber within the
fluidic cartridge to enable on-cartridge Lab-On-Chip
processing.
[0152] In some instances, light delivery schemes are utilized to
provide the optical excitation and/or emission and/or detection of
fold amplification. In certain embodiments, this includes using the
flow cell materials (thermal polymers like acrylic (PMMA) cyclic
olefin polymer (COP), cyclic olefin co-polymer, (COC), etc.) as
optical wave guides to remove the need to use external components.
In addition, in some instances light sources--light emitting
diodes--LEDs, vertical-cavity surface-emitting lasers--VCSELs, and
other lighting schemes are integrated directly inside the flow cell
or built directly onto the micro electrode array surface to have
internally controlled and powered light sources. Miniature PMTs,
CCDs, or CMOS detectors can also be built into the flow cell. This
minimization and miniaturization enables compact devices capable of
rapid signal delivery and detection while reducing the footprint of
similar traditional devices (i.e. a standard bench top
PCR/QPCR/Fluorometer).
Amplification on Chip
[0153] In some instances, silicon microelectrode arrays can
withstand thermal cycling necessary for PCR. In some applications,
on-chip PCR is advantageous because small amounts of target nucleic
acids can be lost during transfer steps. In certain embodiments of
devices, systems or processes described herein, any one or more of
multiple PCR techniques are optionally used, such techniques
optionally including any one or more of the following: thermal
cycling in the flowcell directly; moving the material through
microchannels with different temperature zones; and moving volume
into a PCR tube that can be amplified on system or transferred to a
PCR machine. In some instances, droplet PCR is performed if the
outlet contains a T-junction that contains an immiscible fluid and
interfacial stabilizers (surfactants, etc). In certain embodiments,
droplets are thermal cycled in by any suitable method.
[0154] In some embodiments, amplification is performed using an
isothermal reaction, for example, transcription mediated
amplification, nucleic acid sequence-based amplification, signal
mediated amplification of RNA technology, strand displacement
amplification, rolling circle amplification, loop-mediated
isothermal amplification of DNA, isothermal multiple displacement
amplification, helicase-dependent amplification, single primer
isothermal amplification or circular helicase-dependent
amplification.
[0155] In various embodiments, amplification is performed in
homogenous solution or as heterogeneous system with anchored
primer(s). In some embodiments of the latter, the resulting
amplicons are directly linked to the surface for higher degree of
multiplex. In some embodiments, the amplicon is denatured to render
single stranded products on or near the electrodes. Hybridization
reactions are then optionally performed to interrogate the genetic
information, such as single nucleotide polymorphisms (SNPs), Short
Tandem Repeats (STRs), mutations, insertions/deletions,
methylation, etc. Methylation is optionally determined by parallel
analysis where one DNA sample is bisulfite treated and one is not.
Bisulfite depurinates unmodified C becoming a U. Methylated C is
unaffected in some instances. In some embodiments, allele specific
base extension is used to report the base of interest.
[0156] Rather than specific interactions, the surface is optionally
modified with nonspecific moieties for capture. For example,
surface could be modified with polycations, i.e., polylysine, to
capture DNA molecules which can be released by reverse bias (-V).
In some embodiments, modifications to the surface are uniform over
the surface or patterned specifically for functionalizing the
electrodes or non electrode regions. In certain embodiments, this
is accomplished with photolithography, electrochemical activation,
spotting, and the like.
[0157] In some applications, where multiple chip designs are
employed, it is advantageous to have a chip sandwich where the two
devices are facing each other, separated by a spacer, to form the
flow cell. In various embodiments, devices are run sequentially or
in parallel. For sequencing and next generation sequencing (NGS),
size fragmentation and selection has ramifications on sequencing
efficiency and quality. In some embodiments, multiple chip designs
are used to narrow the size range of material collected creating a
band pass filter. In some instances, current chip geometry (e.g.,
80 um diameter electrodes on 200 um center-center pitch (80/200)
acts as 500 bp cutoff filter (e.g., using voltage and frequency
conditions around 10 Vpp and 10 kHz). In such instances, a nucleic
acid of greater than 500 bp is captured, and a nucleic acid of less
than 500 bp is not. Alternate electrode diameter and pitch
geometries have different cutoff sizes such that a combination of
chips should provide a desired fragment size. In some instances, a
40 um diameter electrode on 100 um center-center pitch (40/100) has
a lower cutoff threshold, whereas a 160 um diameter electrode on
400 um center-center pitch (160/400) has a higher cutoff threshold
relative to the 80/200 geometry, under similar conditions. In
various embodiments, geometries on a single chip or multiple chips
are combined to select for a specific sized fragments or particles.
For example a 600 bp cutoff chip would leave a nucleic acid of less
than 600 bp in solution, then that material is optionally
recaptured with a 500 bp cutoff chip (which is opposing the 600 bp
chip). This leaves a nucleic acid population comprising 500-600 bp
in solution. This population is then optionally amplified in the
same chamber, a side chamber, or any other configuration. In some
embodiments, size selection is accomplished using a single
electrode geometry, wherein nucleic acid of >500 bp is isolated
on the electrodes, followed by washing, followed by reduction of
the ACEK high field strength (change voltage, frequency,
conductivity) in order to release nucleic acids of <600 bp,
resulting in a supernatant nucleic acid population between 500-600
bp.
[0158] In some embodiments, the chip device is oriented vertically
with a heater at the bottom edge which creates a temperature
gradient column. In certain instances, the bottom is at denaturing
temperature, the middle at annealing temperature, the top at
extension temperature. In some instances, convection continually
drives the process. In some embodiments, provided herein are
methods or systems comprising an electrode design that specifically
provides for electrothermal flows and acceleration of the process.
In some embodiments, such design is optionally on the same device
or on a separate device positioned appropriately. In some
instances, active or passive cooling at the top, via fins or fans,
or the like. provides a steep temperature gradient. In some
instances the device or system described herein comprises, or a
method described herein uses, temperature sensors on the device or
in the reaction chamber monitor temperature and such sensors are
optionally used to adjust temperature on a feedback basis. In some
instances, such sensors are coupled with materials possessing
different thermal transfer properties to create continuous and/or
discontinuous gradient profiles.
[0159] In some embodiments, the amplification proceeds at a
constant temperature (i.e, isothermal amplification).
[0160] In some embodiments, the methods disclosed herein further
comprise sequencing the nucleic acid isolated as disclosed herein.
In some embodiments, the nucleic acid is sequenced by Sanger
sequencing or next generation sequencing (NGS). In some
embodiments, the next generation sequencing methods include, but
are not limited to, pyrosequencing, ion semiconductor sequencing,
polony sequencing, sequencing by ligation, DNA nanoball sequencing,
sequencing by ligation, or single molecule sequencing.
[0161] In some embodiments, the isolated nucleic acids disclosed
herein are used in Sanger sequencing. In some embodiments, Sanger
sequencing is performed within the same device as the nucleic acid
isolation (Lab-on-Chip). Lab-on-Chip workflow for sample prep and
Sanger sequencing results would incorporate the following steps: a)
sample extraction using ACE chips; b) performing amplification of
target sequences on chip; c) capture PCR products by ACE; d)
perform cycle sequencing to enrich target strand; e) capture
enriched target strands; f) perform Sanger chain termination
reactions; perform electrophoretic separation of target sequences
by capillary electrophoresis with on chip multi-color fluorescence
detection. Washing nucleic acids, adding reagent, and turning off
voltage is performed as necessary. Reactions can be performed on a
single chip with plurality of capture zones or on separate chips
and/or reaction chambers.
[0162] In some embodiments, the method disclosed herein further
comprise performing a reaction on the nucleic acids (e.g.,
fragmentation, restriction digestion, ligation of DNA or RNA). In
some embodiments, the reaction occurs on or near the array or in a
device, as disclosed herein.
Other Assays
[0163] The isolated nucleic acids disclosed herein may be further
utilized in a variety of assay formats. For instance, devices which
are addressed with nucleic acid probes or amplicons may be utilized
in dot blot or reverse dot blot analyses, base-stacking single
nucleotide polymorphism (SNP) analysis, SNP analysis with
electronic stringency, or in STR analysis. In addition, such
devices disclosed herein may be utilized in formats for enzymatic
nucleic acid modification, or protein-nucleic acid interaction,
such as, e.g., gene expression analysis with enzymatic reporting,
anchored nucleic acid amplification, or other nucleic acid
modifications suitable for solid-phase formats including
restriction endonuclease cleavage, endo- or exo-nuclease cleavage,
minor groove binding protein assays, terminal transferase
reactions, polynucleotide kinase or phosphatase reactions, ligase
reactions, topoisomerase reactions, and other nucleic acid binding
or modifying protein reactions.
[0164] In addition, the devices disclosed herein can be useful in
immunoassays. For instance, in some embodiments, locations of the
devices can be linked with antigens (e.g., peptides, proteins,
carbohydrates, lipids, proteoglycans, glycoproteins, etc.) in order
to assay for antibodies in a bodily fluid sample by sandwich assay,
competitive assay, or other formats. Alternatively, the locations
of the device may be addressed with antibodies, in order to detect
antigens in a sample by sandwich assay, competitive assay, or other
assay formats. As the isoelectric point of antibodies and proteins
can be determined fairly easily by experimentation or pH/charge
computations, the electronic addressing and electronic
concentration advantages of the devices may be utilized by simply
adjusting the pH of the buffer so that the addressed or analyte
species will be charged.
[0165] In some embodiments, the isolated nucleic acids are useful
for use in immunoassay-type arrays or nucleic acid arrays.
Exemplary Comparison
[0166] Approximately 100 ng of input E. coli genome is necessary
for conventional manual methods, (e.g., 50 ng of input DNA is
required for Nextera, assuming 50% recovery (Epicentre WaterMaster
kit claims recovery about 30-60%) from DNA extraction
purification). This is equivalent to about 20 million bacteria. In
some embodiments of the present invention, less than 10,000
bacteria input is sufficient (e.g., since the chip is self
contained and involves less transfers the efficiency is higher). In
some embodiments, this is at least a 100 fold reduction in input,
which can be important for applications where sample is limited,
such as tumor biopsies.
[0167] Table 1 below outlines exemplary steps involved to go from
E. coli to DNA suitable for sequencing. In some instances,
conventional methods require centrifugation, several temperatures,
wash steps, and numerous transfer steps which are inefficient. In
contrast, as described herein, in some embodiments allows the same
steps to be carried out by a device that minimizes the pipette
transfers and exposure to large virgin surfaces with varying
degrees of nonspecific binding properties. In some instances, the
device is temperature controlled to provide appropriate reaction
conditions. In some instances, PCR, cycle PCR for sequencing
pre-amp or full PCR (endpoint, real time or digital) is
accomplished off-device or on-device. Off-device includes not on
the device but on the same cartridge assembly, connections via
fluidic channels or conduits. Furthermore, in some instances PCR
amplification is accomplished in the device flow cell chamber, in a
PCR tube that is on the cartridge, or though fluidic channels that
possess heat zones for temperature cycling. In some instances, the
eluate from the device chamber is combined with side channel(s)
primed with non aqueous miscible fluid, e.g., oil, and other
droplet stabilizers to perform amplification in droplets. In some
embodiments, the temperature cycling mechanics are as described
above.
[0168] In Table 1, the amount of starting material for the
conventional processing was 2-5.times.10.sup.7 E. Coli cells in
approximately 1 ml of water and the entire amount was concentrated
on the filters. Using the chip, as disclosed herein, only
1.times.10.sup.4 E. Coli cells in approximately 50 microliters was
applied to the flow cell. This was 3 orders of magnitude less
starting material.
TABLE-US-00001 TABLE 1 Comparison of methods for nucleic acid
isolation. An exemplary embodiment provided herein Conventional
Epicentre WaterMaster DNA Purification Kit [ON CHIP] Concentrate E.
coli bacteria on filters Capture E. coli, 1 MHz, 10Vpp, 10' Lysis
solution Electro-lyse E. coli, 200 V DC, 1 msec pulse Proteinase K
treatment, 65 C., 15' De-energize electrodes RNase treatment, 37
C., 30' Collection, 10 Vpp, 10 KHz Precipitate protein by
centrifuge, 10K x g, 4 C., De-energize electrodes 10' Wash
isopropanol Q protease treatment, 37 C., 10' Precipitate protein by
centrifuge, 10K x g, 4 C., Inactivate 70 C., 10' 10' Rinse pellet
with 70 ethanol Collection, 10 Vpp, 10 KHz Resuspend DNA in TE
buffer Wash with Nextera LMW buffer Remove inhibitors, 2K x g, 2'
Repeat 2X DNA ready for library prep Epicentre Nextera DNA Sample
Prep (Illumina) 50 ng input DNA (1e7 E. coli equiv.) Fragment with
Transposase, 55 C., 5' Fragment with Transposase, 55 C., 7' Purify
with Zymo spin column, 10K x g, 1' Elute DNA into microtube Add
adapters, cycle PCR, 9 cycles [OFF CHIP] Purify with Zymo spin
column, 10K x g, 1' Add adapters, cycle PCR, 9 cycles Purify with
Zymo spin column, 10K x g, 1' Sequence Sequence
[0169] In various embodiments (i.e., depending on the AC
electrokinetic parameters), cells or other micron scale particles
are concentrated to either the low or high field regions. In some
instances, the crossover frequency which determines whether a
particle moves into or away from the high field region can be tuned
by varying the AC frequency, voltage, medium conductivity,
adulterating particle polarizability (such as attachment or binding
of materials with different DEP characteristics), or electrode
geometry. In some instances, nanoscale particles are limited to
concentration in the high field region. In some instances, Brownian
motion and other hydrodynamic forces limit ability to concentrate
in low field regions.
DEFINITIONS AND ABBREVIATIONS
[0170] The articles "a", "an" and "the" are non-limiting. For
example, "the method" includes the broadest definition of the
meaning of the phrase, which can be more than one method.
[0171] "Vp-p" is the peak-to-peak voltage.
[0172] "TBE" is a buffer solution containing a mixture of Tris
base, boric acid and EDTA.
[0173] "TE" is a buffer solution containing a mixture of Tris base
and EDTA.
[0174] "L-Histidine buffer" is a solution containing
L-histidine.
[0175] "DEP" is an abbreviation for dielectrophoresis.
EXAMPLES
Example 1
Formation of Hydrogel by Spin-Coating (Two Coats) 1
[0176] For a layer of hydrogel, approximately 70 microliters of
hydrogel is used to coat a 10.times.12 mm chip.
[0177] A low concentration (.ltoreq.1% solids by volume) cellulose
acetate solution is dissolved into a solvent such as acetone, or an
acetone and ethanol mixture and applied to an electrode array chip
as disclosed herein. The chip is spun at a low rpm rate
(1000-3000). The low rpm rate ensures that the height of the gel is
in the range of 500 nm or greater.
[0178] The first (bottom) coating of cellulose acetate is dried at
room temperature, in a convection oven, or a vacuum oven.
Optionally, the second layer of cellulose-acetate spin-coat is
added immediately.
[0179] The second layer of cellulose acetate comprises a high
concentration (.gtoreq.2%) of cellulose acetate dissolved into a
solvent such as acetone, or an acetone and ethanol mixture. After a
second layer of cellulose acetate is added, the chip is spun at a
high rpm rate (9000-12000). The high rpm rate will ensure the
height of the gel is in the range of 300 nm or less.
[0180] The chip with two layers of cellulose acetate is then dried
at room temperature, in a convection oven, or in a vacuum oven.
Example 2
Formation of Hydrogel with Additives by Spin-Coating (Two
Coats)
[0181] For a layer of hydrogel, approximately 70 microliters of
hydrogel is used to coat a 10.times.12 mm chip.
[0182] A low concentration (.ltoreq.1% solids by volume) cellulose
acetate solution is dissolved into a solvent such as acetone, or an
acetone and ethanol mixture and applied to an electrode array chip
as disclosed herein. The chip is spun at a low rpm rate
(1000-3000). The low rpm rate ensures that the height of the gel is
in the range of 500 nm or greater.
[0183] The first (bottom) coating of cellulose acetate is dried at
room temperature, in a convection oven, or a vacuum oven.
Optionally, the second layer of cellulose-acetate spin-coat is
added immediately.
[0184] The second layer of cellulose acetate comprises a high
concentration (.gtoreq.2%) of cellulose acetate dissolved into a
solvent such as acetone, or an acetone and ethanol mixture. A low
concentration (1-15%) of conductive polymer (PEDOT:PSS or similar)
is added into the second cellulose acetate solution. After a second
layer of cellulose acetate is added, the chip is spun at a high rpm
rate (9000-12000). The high rpm rate will ensure the height of the
gel is in the range of 300 nm or less.
[0185] The chip with two layers of cellulose acetate is then dried
at room temperature, in a convection oven, or in a vacuum oven.
Example 3
Formation of Hydrogel with Additives by Spin-Coating (Three
Coats)
[0186] For a layer of hydrogel, approximately 70 microliters of
hydrogel is used to coat a 10.times.12 mm chip.
[0187] A low concentration (.ltoreq.1% solids by volume) cellulose
acetate solution is dissolved into a solvent such as acetone, or an
acetone and ethanol mixture and applied to an electrode array chip
as disclosed herein. The chip is spun at a high rpm rate
(9000-12000). The low rpm rate ensures that the height of the gel
is in the range of 300 nm or less.
[0188] The first (bottom) coating of cellulose acetate is dried at
room temperature, in a convection oven, or a vacuum oven.
Optionally, the second layer of cellulose-acetate spin-coat is
added immediately.
[0189] The second layer of cellulose acetate comprises a high
concentration (.gtoreq.2%) of cellulose acetate dissolved into a
solvent such as acetone, or an acetone and ethanol mixture. A low
concentration (1-15%) of conductive polymer (PEDOT:PSS or similar)
is added into the second cellulose acetate solution. After a second
layer of cellulose acetate is added, the chip is spun at a low rpm
rate (1000-3000). The low rpm rate will ensure that the height of
the gel is in the range of 500 nm or greater.
[0190] The second coating of cellulose acetate is dried at room
temperature, in a convection oven, or a vacuum oven. Optionally,
the third layer of cellulose-acetate spin-coat is added
immediately.
[0191] The third layer of cellulose acetate comprises a high
concentration (.gtoreq.2%) of cellulose acetate dissolved into a
solvent such as Acetone, or an Acetone Ethanol mixture. The chip is
spun at a high rpm rate (9000-12000). The low rpm rate ensures that
the height of the gel is in the range of 300 nm or less.
[0192] The chip with three layers of cellulose acetate is then
dried at room temperature, in a convection oven, or in a vacuum
oven.
Example 4
Chin Construction
[0193] For FIGS. 2 & 3: A 45.times.20 custom 80 .mu.m diameter
circular platinum microelectrode array on 200 um center-center
pitch was fabricated based upon previous results (see references
1-3, below). All 900 microelectrodes are activated together and AC
biased to form a checkerboard field geometry. The positive DEP
regions occur directly over microelectrodes, and negative low field
regions occur between microelectrodes. The array is over-coated
with a 200 nm-500 nm thick porous poly-Hema hydrogel layer
(Procedure: 12% pHema in ethanol stock solution, purchased from
PolySciences Inc., that is diluted to 5% using ethanol. 70 uL of
the 5% solution is spun on the above mentioned chip at a 6K RPM
spin speed using a spin coater. The chip+hydrogel layer is then put
in a 60.degree. C. oven for 45 minutes) and enclosed in a
microfluidic cartridge, forming a 50 .mu.L sample chamber covered
with an acrylic window (FIG. 1). Electrical connections to
microelectrodes are accessed from Molex connectors from the PCB
board in the flow cell. A function generator (HP 3245A) provided
sinusoidal electrical signal at 10 KHz and 10-14V peak-peak,
depending on solution conductivity. Images were captured with a
fluorescent microscope (Leica) and an EGFP cube (485 nm emission
and 525 nm excitation bandpass filters). The excitation source was
a PhotoFluor II 200W Hg arc lamp. [0194] [1] R. Krishnan, B. D.
Sullivan, R. L. Mifflin, S. C. Esener, and M. J. Heller, [0195]
"Alternating current electrokinetic separation and detection of DNA
nanoparticles in high-conductance solutions." Electrophoresis, vol.
29, pages 1765-1774, 2008. [0196] [2] R. Krishnan and M. J. Heller,
"An AC electrokinetic method for enhanced detection of DNA
nanoparticles." J. Biophotonics, vol. 2, pages 253-261, 2009.
[0197] [3] R. Krishnan, D. A. Dehlinger, G. J. Gemmen, R. L.
Mifflin, S. C. Esener, and M. J. Heller, "Interaction of
nanoparticles at the DEP microelectrode interface under high
conductance conditions" Electrochem. Comm., vol. 11, pages
1661-1666, 2009.
Example 5
Isolation of Human Genomic DNA
[0198] Human Genomic DNA (gDNA) was purchased from Promega
(Promega, Madison, Wis.) and was sized to 20-40 kbp. (Sizing gel
not shown.) The gDNA was diluted in DI water to the following
concentrations: 50 nanograms, 5 nanograms, 1 nanogram, and 50
picograms. The gDNA was stained using 1.times.SYBR Green I green
fluorescent double stranded DNA dye purchased from Invitrogen (Life
Technologies, Carlsbad, Calif.). This mixture was then inserted
into the microelectrode arrays and run at 14 Volts peak to peak
(Vp-p), at 10 kHz sine wave for 1 minute. At the conclusion of 1
minute, a picture of the microelectrode pads was taken using a CCD
camera with a 10.times. objective on a microscope using green
fluorescence filters (FITC) so that the gDNA could be visualized
(FIG. 2) The chip was able to identify down to 50 pg of gDNA in 50
.mu.L water, i.e. 1 ng/mL concentration. Additionally, at 50
picograms, each microelectrode had on average .about.60 femtograms
of DNA since there are 900 microelectrodes on the array. The
low-level concentration ability of the ACE device is well within
the range of 1-10 ng/mL needed to identify Cfc-DNA biomarkers in
plasma and serum (see references 4-6 below). [0199] [4] T. L. Wu et
al, "Cell-free DNA: measurement in various carcinomas and
establishment of normal reference range." Clin Chim Acta., vol. 21,
pages 77-87, 2002. [0200] [5] R. E. Board et al, "DNA Methylation
in Circulating Tumour DNA as a Biomarker for Cancer", Biomarker
Insights, vol. 2, pages 307-319, 2007. [0201] [6] O. Gautschi et
al, "Circulating deoxyribonucleic Acid as prognostic marker in
non-small-cell lung cancer patients undergoing chemotherapy." J
Clin Oncol., vol. 22, pages 4157-4164, 2004.
Example 6
Isolation of DNA from E. Coli
[0202] Using the Chip and methods described in Examples 4 and 5,
approximately 5000 green fluorescent E. coli cells in 50 uL of
fluid was inserted into a chip and run using protocol described in
caption for FIG. 3. Panel (A) shows a bright field view. Panel (B)
shows a green fluorescent view of the electrodes before DEP
activation. Panel (C) shows E. coli on the electrodes after one
minute at 10 kHz, 20 Vp-p in 1.times.TBE buffer. Panel (D) shows E.
coli on the electrodes after one minute at 1 MHz, 20 Vp-p in
1.times.TBE buffer.
[0203] The E. coli depicted in FIG. 3 were lysed using a 100
milli-second 100V DC pulse using the HP 3245A function generator.
The lysed particulates were then gathered on the electrode surface
using 10 kHz, 10Vp-p and the Illumina Nextera Protocol was used for
library prep for sequencing while the DNA was on the chip (by
inserting the appropriate buffers at the appropriate times onto the
chip) to tag the DNA for Sequencing. The DNA was then eluted in 50
uL of 1.times.TBE Buffer and then PCR amplified for 9-12 cycles
(using the Nextera Protocol) on a Bio-Rad PCR machine. The
amplified DNA was then run on an Illumina GA II Sequencer. DNA from
E. Coli was also isolated from 1.times.TBE buffer (10 million
cells) using the Epicentre.TM. WaterMaster.TM. DNA purification
procedure, to serve as a gold standard for comparison. The results
are depicted in FIG. 4.
Example 7
Formation of Hydrogel with GVD
[0204] Hydrogel, such as polyhydroxyethylmethacrylate(pHEMA) may
also be layered onto the chip surface via vapor deposition using
proprietary assays developed by GVD Corporation (Cambridge, Mass.)
(see www.gvdcorp.com). Hydrogels such as pHEMA were deposited in
various thickness (100, 200, 300, 400 nm) and crosslinking (5, 25,
40%) density on electrode chips was performed using technology
developed by GVD Corporation. The hydrogel films were tested using
a standard ACE protocol (no pretreatment, 7Vp-p, 10 KHz, 2 minutes,
0.5.times.PBS, 500 ng/ml gDNA labeled with Sybr Green 1).
Fluorescence on the electrodes was captured by imaging. FIG. 10
shows that 100 nm thickness, 5% crosslink gel device was found to
have strong DNA capture. The process could also be optimized by
changing the deposition rate or anchoring growth to the surface of
the microelectrode array (i.e., to the passivation layer and
exposed electrodes), using an adhesion promoter such as a silane
derivative.
Example 8
Performance of Disclosed Device and Method v. Conventional
Method
[0205] QIAGEN.RTM. circulating nucleic acid Purification kit
(cat#55114) was used to purify 1 ml of plasma from chronic
lymphocytic leukemia (CLL) patients, according to manufacturer's
protocol. Briefly, incubation of 1 ml plasma with Proteinase K
solution was performed for 30 minutes at 60.degree. C. The reaction
was quenched on ice and the entire volume was applied to a QIAamp
Mini column connected to a vacuum. The liquid was pulled through
the column and washed with 3 different buffers (600-750 ul each).
The column was centrifuged at 20,000.times.g, 3 minutes and baked
at 56.degree. C. for 10 minutes to remove excess liquid. The sample
was eluted in 55 .mu.l of elution buffer with 20,000.times.g, 1
minute centrifugation. Total processing time was .about.2.5
hours.
[0206] The chip die size was 10.times.12 mm, with 60-80 .mu.m
diameter Pt electrodes on 180-200 .mu.m center-to-center pitch,
respectively. The array was overcoated with a 5% pHEMA hydrogel
layer (spun cast 6000 rpm from Ethanol solution, 12% pHEMA stock
from Polysciences). The chip was pretreated using 0.5.times.PBS, 2V
rms, 5 Hz, 15 seconds. The buffer was removed and 25 .mu.l of CLL
patient plasma was added. DNA was isolated for 3 minutes at 11 V
p-p, 10 Khz, then washed with 500 .mu.l of TE buffer at a 100
.mu.l/min flow rate, with power ON. The voltage was turned off and
the flow cell volume was eluted into a microcentrifuge tube. Total
processing time was .about.10 minutes.
[0207] The same process can be applied to fresh whole blood without
modification. Ability to extract and purify DNA from whole
undiluted blood is uniquely enabled by the chip technology
disclosed herein.
[0208] DNA quantitation was performed on the Qiagen and chip elutes
using PicoGreen according to manufacturer's protocol (Life Tech)
(Table 2).
[0209] Subsequent gel electrophoresis, PCR and Sanger sequencing
reactions showed similar performance for both extraction techniques
with the chip being able to process whole blood as well as plasma.
Mann-Whitney U non-parametric statistical test was also run between
DNA amounts isolated from plasma using the Qiagen and chip
techniques. There was no statistical difference (p<0.05
two-tailed) using either method of DNA purification.
TABLE-US-00002 TABLE 2 DNA purification, chip v. Qiagen Values are
in ng/ml and normalized to original plasma sample volume for
comparison purposes. Chip - Qiagen - Chip - Patient plasma plasma
blood normal A 139 39 274 normal B 206 80 114 normal C 133 32 97
TJK 528 320 547 167 TJK 851 218 393 307 TJK 1044 285 424 794 TJK
334 261 1387 666 TJK 613 179 53 257 TJK 762 145 367 314 TJK 847 886
1432 811 TJK 248 84 119 448 TJK 1024 302 169 332 TJK 1206 584 396
1435 TJK 1217 496 146 584 TJK 1262 87 84 1592 TJK 1311 119 257
1825
[0210] While preferred embodiments of the present invention have
been shown and described herein, it will be obvious to those
skilled in the art that such embodiments are provided by way of
example only. Numerous variations, changes, and substitutions will
now occur to those skilled in the art without departing from the
invention. It should be understood that various alternatives to the
embodiments of the invention described herein may be employed in
practicing the invention. It is intended that the following claims
define the scope of the invention and that methods and structures
within the scope of these claims and their equivalents be covered
thereby.
* * * * *
References